Patent Grant
7220229
This invention generally relates to a device and method for monitoring fluid properties, and specifically relates to a density/solute monitor having ultrasound probes for continuous monitoring of the ultrasound velocity of fluid in a biological or chemical processing system in order to determine fluid density, compressibility, solute concentration, and the fluid flow and a method for using the same wherein the probes are integrated with modality measurements such as optical absorbance, conductivity, impedance, magnetic resonance, radiation attenuation, and tracers of fluid.
Two classical methods of measuring density of a fluid include: 1) measuring the weight of fluid in a flask of fixed volume; and 2) employing the buoyancy of a density float for the assessment of fluid density. Both of these methods require collection of large samples from a fluid-processing device such as a pipeline or reactor for off-line measurements. For a given solution, density relates to the solute concentration of the solution. Although the density measurement is not specific to what solute is in the solution, these two density measurement methodologies and others to be described later have been used as a means to assess solute concentration.
A mechanical device based on resonance has been available to measure density of a fluid sample or that of a flowing fluid on-line. The device has a hollow U-tube with its two ends fixed on a heavy base. The fluid can be infused to fill the U-tube or made to flow along the tube. By measuring the frequency that the U-tube resonates, one then determines the mass of fluid in the U-tube. Since its volume is fixed, the mass is converted to the fluid density. This mechanical density measuring system (MDMS) has high sensitivity and reproducibility in the dynamic measurement of fluid density.
As a fourth density measurement method, one measures the sound velocity of fluid for the determination of the compressibility and density of fluid. Krivitski, in U.S. Pat. Nos. 5,453,576 and 5,685,989 describes an apparatus and method for measuring several hemodynamic parameters by using a sound velocity sensor. The ultrasound transducer is excited to emit a pulse of ultrasound. After its passage through a fluid medium such as the blood, a receiving transducer senses the ultrasound pulse. A protocol to compare the excitation and receiving ultrasound signals determines the transmission time through the blood and subsequently its sound velocity. The information contained in the '576 and the '989 patent is incorporated by reference as though cited in its entirety. When their device is used to measure blood density change for the computation of blood volume, a linear approximation of a non-linear relationship is employed to convert the sound velocity to the density of the blood. Furthermore, the device of the '576 patent has limited sensitivity so as to require the imposition of a large change in blood density for accurate assessment of blood volume.
The system patented by Schneditz in U.S. Pat. No. 5,830,365 also utilizes sound velocity for the measurement of transmission time delay through the blood and then its total protein concentration. A clinical protocol to change the ultrafiltration rate as a patient undergoing hemodialysis treatment is described to produce the change in density, which is assessed through a sound velocity monitor. An equation is deduced to compute from the change measurement the blood volume circulating in the patient. The monitor to measure density is about one order of magnitude less sensitive than that provided by the MDMS or our density/solute monitor. As a result, the application of Schneditz's method to measure blood volume is limited to cases that the change in sound velocity being imposed through the clinical protocol is large.
The fifth density measurement method employs the attenuation due to the absorption of radioactivity by the fluid as a means to assess its density. Approval by regulatory agency is required for this method.
The present invention is directed to a density/solute monitor including an ultrasound probe and a signal processing unit for accurately and reliably determining the phase shift of ultrasound transmission through a fluid and then the sound velocity of the fluid and a method of applying the same to biological or chemical processing systems. A set of equations and measurements by other modalities are incorporated to deduce from the sound velocity the compressibility, density, concentration of specific solute, and concentration of particulate matters of the fluid. The monitor can be used to determine the mass flow of solute, to improve the performance of chemical processes, and to optimize process design. The improvement and optimization can lead to more efficient collection of solutes, more solute purity in the collection, and better efficiency of the chemical processes.
The novel embodiments of the density/solute monitoring system include a signal processing unit with simple hardware and software to determine at high accuracy phase shift and transmission time of ultrasound signals; a two-fluid calibration procedure to convert the phase shift and transmission time in terms of sound velocity; an appropriate placement of the probe to time the passage of certain solute injected upstream of the probe; the use of two probes in series to measure volume flow; a procedure to work with the MDMS for the establishment of an empirical relation between the density and sound velocity of fluid and to account for the dependence on temperature; the calculation of the compressibility of the fluid to derive its relation with the sound velocity and density of the fluid; a set of computer files and equations specific to given solute, solution and density/solute monitor on the conversion of density to the solute concentration in the solution.
The ultrasound probe can work alone or in combination with other detection modalities to achieve more functionality for the density/solute monitor. Other detection modalities include:
By making use of the high sensitivity of the ultrasound probe, the multi-modality monitor gains additional power to determine the concentration of specific solute in the solution, the passage of specific solute through a chromatography column, and the dynamic changes of the solute in chemical or biological processing systems. In applying these probes and methods to paper, petroleum, chemical, pharmaceutical, food and bioprocessing industry; the engineers can determine more accurately the mass flow being transported through pipeline, achieve better solute purity in solution collected from chromatography column, and control more responsively the chemical or biological processing. The multi-modality methodology is applicable to human for determinations of blood parameters, vascular functions, and cardiac performance. The information provides key measurements for physicians to maintain homeostasis of the patient and to diagnose or to prevent cardiac deficiencies such as hypotension and shock in patients undergoing hemodialysis treatment or subject to trauma or burns.
Multi-modality probes and methods are described:
Transducers 22 and 24 are part of said ultrasound probe, which is attached to a signal processing unit. The signal processing unit is comprised of a function generator 20, an amplifier 68, a dual channel analog-to-digital (A/D) converter 70, an interface processor 72, and a computing mechanism 74 as shown in
This power signal is also digitized as an excitation signal by one channel of the dual channel (A/D) converter 70 within the ultrasound signal-processing unit. When the excitation frequency of the excitation signal is chosen as 5 Megahertz, the emitting transducer emits ultrasound at the frequency of 5 Megahertz. The sampling frequency of the A/D converter is chosen to be an integer multiple of the excitation frequency. This integer is designated as m. For an ultrasound/excitation frequency of 5 Megahertz and an A/D converter's sampling frequency (fsampling) of 65 mega samples per second (MSPS), m is 13, meaning there are 13 digitized samples over one full ultrasound oscillation. Or, if an A/D converter with a sampling frequency of 105 MSPS is used, m will be 21. When low cost A/D converters at higher sampling frequencies become available, the ultrasound frequency or the number of samples per oscillation cycle can be increased to improve the resolution of the density/solute monitor. The receiving transducer 24 receives the ultrasound wave after its passage through the fluid. The signal is amplified by amplifier 68 and digitized through the other channel of the dual channel A/D converter 70. Both the digitized excitation and receiving signals are sent to the interface processor 72 for storage and a computing system 74 for analysis.
The system of the present invention uses continuous measurements of phase shift and transmission time of ultrasound waves in a fluid to assess sound velocity, density, solute concentration, compressibility, and changes in these quantities. Once the ultrasound probe is inserted into a fluid and the signal processing unit described above transmits and digitizes ultrasound waves through the fluid, the computing system 74 is ready to determine phase shift and transmission time. The transmission time (Tshift) depicted in
or
Let us identify the excitation and receiving samples stored on the interface processor as Ei and Ri respectively with i being the sampling index. Once some 1000 to 2000 samples from each signal are stored, the computer instructs the interface processor to transfer the data for processing. First, their average is determined and subtracted to achieve a zero average. Then the data are multiplied and summed as specified by Equation 3 and 4.
M1=Σ(EiRi) with the summation from i=1 to N Equation 3
M2=Σ(EiRi+j) with the same summation as above Equation 4
where j is chosen so that the receiving signal is shifted by about one quarter of a cycle. It is
j=Round(m/4) Equation 5
The function Round stands for the nearest round off of a number to an integer. The total number N used for the summation is chosen to be an integer multiple of m and to cover most of the period over which we have values for the receiving signal. When the number of cycles to be covered is larger than 60, our computation results indicate good sensitivity in sound velocity determination will be achieved. With M1 and M2 so calculated, we determine the phase shift of the receiving signal from the emitting signal (φ) as:
φ=tan−1[M2/(M1 sin θ)−cot θ] Equation 6
where φ and θ are expressed in the unit of degree and θ is 360°·(j·fultrasound/fsampling). If m is a multiple integer of 4, then θ=90° and Equation 6 reduces to the one commonly used in phase lock computation:
φ=tan−1[M2/M1] Equation 7
Two fluids typical to certain fluid processing will be used to calibrate the probe in the factory or in situ. Let the sound velocity of the two calibrating fluids be c1 and c2 and the corresponding phase shift be φ1 and φ2. The time for the ultrasound to transmit from the emitting transducer through the fluid to the receiving transducer relates the measured phase shift by these equations:
(n+φ1/360°)T0=L/c1 Equation 8
(n+φ2/360°)T0=L/c2 Equation 9
where L is the distance between the transducers for this insertion probe. Suppose the sound velocity of the fluid designated for the measurement is c3 and the measured phase shift is φ3. Then they are related by
(n+φ3/360°)T0=L/c3 Equation 10
Equations 8, 9 and 10 can be reorganized to yield Equation 11 to determine c3 from φ3:
c1/c3=1−(1−c1/c2)(φ3−φ1)/(φ2−φ1) Equation 11
Using a series of fluid samples having a range of solute concentration, we can use the ultrasound probe and the MDMS to determine the sound velocity (c) and the density (ρ) respectively. It is known that the compressibility (κ) of the fluid relates to sound velocity and density by
κ=ρ/c2 Equation 12
By plotting the measurements and calculations against each other, we obtain a set of empirical equations for converting the measured sound velocity in terms of density, compressibility, or solute concentration.
For most cases in industrial and clinical application, the difference among the three sound velocities is smaller than a few percentages. Thus, we can linearize Equation 11 to relate the sound velocity to phase shift by:
c3=c1+(c2−c1)(φ3−φ1)/(φ2−φ1) Equation 13
Since the change of density is also smaller than a few percentages, the change in density and that in sound velocity can be related through a linear equation. Accordingly, Equation 13 can be converted to the following form for the determination of density:
ρ3=ρ1+(ρ2−ρ1)(φ3−φ1)/(φ2−φ1) Equation 14
where ρ3 is the density being measured, and ρ1 and ρ2 the density of the calibrating fluids. In the case of protein solution, the density is linearly related to the concentration of protein C. If the fluid in the pipeline or chemical reactor also has its solute concentration linearly related to the density, we have Equation 15 to derive from the phase shift measurements the solute concentration C3:
C3=C1+(C2−C1)(φ3−φ1)/(φ2−φ1) Equation 15
In the special case that the solute concentration for one calibrating fluid C1 is zero, Equation 15 is simplified to:
C3=C2(φ3−φ1)/(φ2−φ1) Equation 16
Equation 13 is regarded as a two-constant calibration equation of the probe or probes of the monitoring system to convert phase φ3 to c3. In this equation, c1 is given and the two constants are φ1 and (c2−c1)/(φ2−φ1). These two constants are determined by the two fluid calibration procedure. In the same way, one can define the two constants in equation 14 or 15 for converting phase to density or solute concentration respectively.
A signal processing procedure similar to the probe calibration discussed above is applicable to the case where the emitting ultrasound is identical to the excitation signal, i.e. without the gating shown in
The equations derived for the insertion probe are applicable to the cuvette mode of the ultrasound solute probe as shown in
The clip-on mode of the ultrasound probe depicted in
Pipeline, tubing, or chromatography columns with a diameter other than 6.2 mm can also be used in the system and the dimensioning adjustments to the clip will be obvious to those skilled in the art. The resulting adjustment to convert phase shift to density or solute concentration will be incorporated through the parameters stored in a data file accompanying the probe. To gain a larger receiving signal, one can employ a lower ultrasound frequency such as 1 Megahertz to power the emitting transducer. With the sampling frequency remaining at 65 MSPS, one will have 65 samples digitized over one period of oscillation while the total number of samples used in the determination of phase shift may remain in the range of 1000 to 2000.
When the insertion or clip-on mode of the solute monitor is mounted onto the end of a column of chromatography process to assess solute concentration, we note that the transmission time includes that through the column wall, the porous beads in the column and the fluid. The presence of the beads will alter the relation between the fluid density and phase shift, which can be resolved by the on-line calibration procedure described later.
In application, the ultrasound probe of insertion mode is inserted into a fluid processing system such as a pipeline or chemical processing system for continuous measurement of the phase shift of ultrasound transmission in the fluid. In addition, a test fluid with a density ρtest at a volume ΔV is injected into the system upstream of the probe. Let the flow be Q and the volume of fluid situated between the injection and measurement site be V1. According to the density dilution theory, one deduces from the principle of mass conservation the relation specified in Equation 17
Q∫(ρ0−ρ)]dt=ΔV(ρ0−ρtest) Equation 17
where ρ is the density being measured, ρ0 the steady state density before the injection, and the integration limit is over the time that the density is transiently deviated from the steady state density. Corrections can be made for the integration when the injected fluid re-circulates back through the probe. With most small injections, the density change from ρ0 is small.
Equation 14 can be re-expressed as a linear relation between density change Δρ and the phase change Δφ with a calibration constant b1, i.e.
Δρ=b1Δφ Equation 18
Its substitution into Eq. 17 yields Equation 19 for in situ, on-line determination of the calibration constant
b1=(ΔV/Q)(ρtest−ρ0)/∫Δφdt Equation 19
Using Equation 14, one can convert Equation 17 to Equation 20:
Q=ΔV(φtest−φ0)/{∫(φ−φ0)dt} Equation 20
where ρ0, ρtest, ρ, φ0, φtest and φ are respectively the replacements of ρ1, ρ2, ρ3, φ1, φ2 and φ3 in Equation 14. Equation 20 can therefore be used for the calculation of the flow
The consideration on mean transit time, volume and flow in the density dilution theory yields Equation 21 to relate the volume and flow:
Q=V1∫(φ−φ0)dt/{∫(φ−φ0)tdt} Equation 21
From Equation 20 and 21, we can solve for the value of φtest when the flow and volumes are known. The difference between the solute concentration in the flowing fluid and that in the test fluid can now be related to the difference between φtest and φ0.
As another alternative to measure the flow, one can place two probes in two locations along the pipeline or chemical processing system. The flow can be calculated as:
Q=V4-5∫(φ4−φ0)dt}/{∫(φ5−φ4)tdt} Equation 22
where V4-5 is the fluid volume of the pipeline or chemical system in between the two probes, φ4 is the phase shift measured by the upstream probe, and φ5 that by the downstream probe.
There are several working models of the ultrasound system to assess blood density. In one signal processing embodiment the transducer 22 of
In another embodiment, the signals from the receiving transducer and the function generator, which excites the emitting transducer, are processed by a phase lock amplifier such as Stanford Research System SR 844, which is powerful in processing signals with a frequency as high as 200 Megahertz. Many digitized samples from the continuous ultrasound are employed for the calculation. At the ultrasound frequency of interest here, the use of SR 844 provides sensitivity about one order of magnitude higher than the pulse system described previously.
In our preferred embodiment, the ultrasound probe is used in conjunction with a novel ultrasound signal processing unit, a new computation scheme, and a two-fluid calibration procedure. This new scheme is an improved version of the system described in U.S. Pat. No. 6,740,036 as we relax the requirement that the value of m in Equation 5 must be an integer multiple of 4. In the current invention, the digitized data of some 100 oscillations (or 1000 to 2000 digitized samples) are employed. In comparison with the pulse procedure, the use of more samplings for signal processing enables us to gain higher sensitivity in phase shift determination.
As in the SR 844 phase lock amplifier, the 90-degree shift of the excitation or receiving signal in Equation 4 is accomplished by electronic means. Our scheme achieves the shift by shifting the index of digitized receiving signals for multiplications and summations. Since the shift in general may not be exactly 90-degree, the more general Equation 7 is deduced to carry out the computation of the phase shift between the emitting and receiving signal. Our test results indicate that our signal processing unit and the use of Equation 3, 4 and 6, even with a sampling rate of 65 MSPS (or about 15 ns a sample), can achieve a phase resolution of the order 0.03 ns, which is comparable to that via the SR844 amplifier. Only with this sensitivity, can the density and solute concentration expected to occur in industrial and clinical applications be measured.
Because of the new algorithm and the simplicity in hardware design, our invention is in the position of being built as an IC chip. The end result of the use of IC chip will be a monitor with a much lower manufacturing cost than a system using SR 844 phase lock amplifier to process the signals.
The solutes in the solution may exhibit different characteristics to absorbance or reflectance at various wavelength of the light. In a preferred embodiment, the ultrasound probe of the monitoring system works in conjunction with a light-emitting mechanism such an optical detector or a spectrophotometer to measure the absorbance and/or reflectance of fluid in the monitoring system. An optical detector preferably comprises at least one light source and filter and at least two photomultipliers. The spectrophotometer preferably comprises at least one light emitting diode and at least two photodiodes. Conventionally, optical modality requires the detector be calibrated with solutions of different solute concentration. However, as described later, one can employ the ultrasound probe and the on-line procedure to calibrate the optical modality. Let us illustrate this procedure with blood as the fluid and the optical modality being an IR detector. At an appropriate IR frequency, the detector has been used to assess hematocrit, the volumetric percentage of red blood cells in blood.
In clinical practice, the monitors are mounted onto the hemodialysis circuit, which withdraws blood from an artery and returns the blood after its passage of the hemodialysis machine back to a vein of the patient. A bolus of isotonic saline is injected into the circuit to flow through the hemodialysis machine and then the monitors. The sound velocity of saline is lower than that of blood. The passage of the saline after its mixing with the circulating blood will be recognized by the density monitor as a reduction in phase shift. Since there are no red blood cells in saline, we also expect to see a transient decrease in hematocrit, which will be picked up by the IR detector because of the resulting change in absorbance or reflectance characteristics of blood. Let us express the measurement of the optical detector as optical density (OD). When the blood is mixed with a saline of density ρs and no red blood cells, the dilution of the density (ρb) and hematocrit (H) of blood follow Equation 21.
(ρb−ρs)=[(ρb,1−ρs)/H1]H Equation 21
where ρb,1 is the steady-state blood density and H1 is the steady-state hematocrit before the saline injection.
By plotting the change in optical density ΔOD against that of density Δρb as detected through the ultrasound probe, we can obtain the slope b2 in the linear relation of Equation 22:
Δρb=b2ΔOD Equation 22
Its combination with Equation 21 for saline dilution yields Equation 23:
ΔH/H1=[b2/(ρb,1−ρs)]ΔOD Equation 23
In practice, the optical detector is located, for example, downstream of the ultrasound probe. To carry out the data analysis through Equation 22, we will adjust the optical signal by a time for which the linear fit between the optical density and density has the correlation coefficient closest to unity. Then the slope of this linear fit is taken as b2. Once the slope is measured with this on-line procedure, Equation 23 is the calibration equation to convert the change in optical density to the hematocrit ratio (ΔH/H1).
In industrial applications, the injectate may contain a number of solutes of interest to the chemical and biological process. Each solute may have different absorbance or reflectance characteristics. Thus the spectrum of the optical detector will be set up to differentiate the absorbance or reflectance of the solutes. Because of difference in molecular sizes or activities, the passage of these solutes through the chemical system, biological reactor or chromatography column may occur at various times. Their presence in the flowing fluid will alter the phase shift and light absorbance as the fluid passing through the monitor. A procedure similar to hematocrit calibration can be applied as an on-line means to calibrate the optical detector in industrial setting. Conversely, the specificity of the optical detector in solute identification allows us to pinpoint which passage detected by the ultrasound probe is associated with which specific solute.
The passage of solute as detected by the ultrasound probe can now be used to activate a fractional collector to collect the solution containing most of the specific solute. This on-line control will reduce the collection of other solutes coming through the probe at other times and to improve the purity of the specific solute in the collection. This characteristic to identify the presence of solutes through the use of density/solute monitor can also be used to improve the collection of solution containing no solutes for reuse by the chromatography process.
γray is absorbed by the fluid over its passage. The attenuation of γ ray, a physical characteristic of the fluid, can be associated with and thus be used to determine the density of the fluid. The combination of this attenuation with the ultrasound characteristics may further enhance our ability to differentiate the kind of fluid flowing pass the density/solute monitor.
Infusion of hypertonic saline has been used clinically to extract fluid from the tissue in human body to the circulation. The extracted fluid has a density lower than the blood. Thus its mixing with blood will lower the density of blood. Consequently, multi-modality monitor on conductivity and phase shift may allow us to assess the process of fluid extraction from the tissue.
Tracers have been used to monitor dynamic events occurring in a chemical system, pipeline, or the human circulation system. Some tracers can be detected by magnetic resonance imaging (MRI) system or CT scan. If the tracers are in the form of vesicles containing a fluid or other medium that its density is different from that of the flowing fluid, then the density or compressibility of fluid may be altered by the presence of tracers and be detected by the density monitor. The tracer can be a substance tagged with radioactive element or dye. Radioactivity counter can detect the former and optical detector set at the frequency most sensitive to the dye can detect the latter. The use of multi-modality detection systems and tracers may further improve the sensitivity and specificity of the density/solute monitor to better track the movement of solutes through chemical processing system or human circulation.
This application is a continuation-in-part of Ser. No. 10/274,086, filed Oct. 18, 2002, now U.S. Pat. No. 6,740,036, filed Oct. 18, 2002 and issued on May 25, 2004, which is continuation-in-part of Ser. No. 09/908,223, filed Jul. 18, 2001, now of U.S. Pat. No. 6,485,427 B1, filed Jul. 18, 2001 and issued on Nov. 26, 2002, and U.S. Provisional Application 60/218,906, filed Jul. 18, 2000.
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| 5959601 | Ho et al. | Sep 1999 | A |
| 6390999 | Zscheile et al. | May 2002 | B1 |
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| Number | Date | Country | |
|---|---|---|---|
| 20040087860 A1 | May 2004 | US |
| Number | Date | Country | |
|---|---|---|---|
| 60218906 | Jul 2000 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 10274086 | Oct 2002 | US |
| Child | 10689450 | US | |
| Parent | 09908223 | Jul 2001 | US |
| Child | 10274086 | US |
