Patent Application
20060010963
1. Field of the Invention
The present invention relates generally to the field of viscosity measurement and more particularly to dynamic measurement of viscosity and density of fluids using magnetostrictive particle sensors.
2. Description of the Prior Art
There are numerous field applications that require precision dynamic measurement of viscosity or density of fluids. They include point-of-care measurement of blood coagulation, detection of gases in ambient air, gas chromatography, and liquid chromatography.
Previous investigators have used piezoelectric material-based systems for viscosity and density measurements.
Although some instruments are known in the art, there exists a need for a more accurate and economical system that can measure the viscosity and density in real time, especially for point-of-care and end-user applications. What is badly needed is a high precision, dynamic viscosity and density measurement system that exploits the unique features of magnetostrictive material.
Magnetostrictive material is usually an alloy of terbium, dysprosium and ferrite. Magnetostriction is the property that causes the magnetostrictive material to change physical shape in the presence of an applied magnetic field. Terfenol-D is a commercially available magnetostrictive material discovered by the Naval Ordnance Laboratory. Terfenol-D can elongate up to around 2000 ppm when subjected to magnetic field so around 2500 Orested. In addition, when a magnetostrictive material is mechanically loaded, it self-generates a magnetic field. If the loading is the result of an applied magnetic field, the total field is the superposition of the applied field and the self-generated field.
These two modes of operation allow magnetostrictive material to convert mechanical energy to magnetic energy and to convert magnetic energy to mechanical energy.
The present invention relates to a liquid viscosity or density measurement system where a liquid sample is measured by means of a magnetic field source that is applied to the liquid creating an applied magnetic field that permeates the liquid. Magnetostrictive particles are placed in contact with said liquid or in a structure that is in contact with the liquid. The magnetic field also permeates the magnetostrictive particles. An output coil is placed in proximity to the magnetostrictive particles where it senses the total magnetic field and produces a voltage proportional to the viscosity of said liquid. Normally the applied magnetic field changes in time and is sinusoidal.
Certain illustrations and figures have been presented to better aid in the understanding of the present invention. The scope of the present invention is not limited to the figures.
A system for magnetostrictive dynamic viscosity and density measurement of fluids can be configured in different ways depending on the application. One representative application is the measurement of blood coagulation or clotting time.
A test tube 1 containing blood 2 (or other liquid), coagulation agent 2, and a predetermined quantity of magnetostrictive particles 3 of a known size can be inserted a magnetostrictive dynamic viscosity and density measurement system. The magnetostrictive particles 3 can be used as is or sealed in a thin polymer shell that is compatible with the fluids to be tested (does not react with them). The particles can also be briskly shaken and sieved to improve the uniformity before being used. An excitation coil 6 can be energized by passing a current 7 (usually sinusoidal) through the coil. Alternating currents which may be sinusoidal will establish a carrier or applied magnetic field in the tube 1 and its ingredients. Since magnetostrictive particles' permeability is higher than that of the tube and the other ingredients, most of the magnetic field lines pass through the magnetostrictive particles.
The magnetostrictive particles 3 can respond in two ways: 1) align along the central axis of the excitation coil creating a least reluctance magnetic field path, and 2) elongate in the direction of the magnetic field due to their unique magnetostriction property. These two phenomena follow the changing magnetic field.
A sensing coil 8 can be placed around the test tube 1. This sensing coil can produce an output voltage 9 at its output proportional to the rate of change of total magnetic flux through it. The time-varying magnetic field from the excitation coil 6 induces a first component of the output voltage across the sensing coil 8. A second component of the output voltage is produced by what is known as the “Villari Effect” where the magnetostrictive material generates a magnetic field when it is mechanically loaded. The first component depends on the geometry of the coil and the permeability of the tube and its ingredients (excluding the magnetostrictive particles). Since these factors remain constant during the coagulation process, the first component of the output voltage merely reflects the driving current 7 in the excitation coil 6.
The second component of the output voltage 9 depends on the stress level and permeability of the magnetostrictive particles. The stress level in the magnetostrictive particles 3 in turn depends on the strength of the driving magnetic field and how much physical resistance to expansion and contraction that the viscosity of the fluid 2 exerts on them. As the fluid coagulates, the viscosity increases. In the case of blood, this is caused the formation of a fibrin network in the clotting blood. As the apparent viscosity of the fluid increases, there is increased physical resistance to expansion and contraction. This phenomenon causes a voltage change at the sensor coil output 9. The change in voltage level can be nearly directly proportional to viscosity changes occurring in the fluid 2. This offers a convenient way to measure the viscosity dynamically without interfering with the formation of the fibrin network, and hence monitor the progress and time of the coagulation process.
The movement of the magnetostrictive particles 3 do to the changing (possibly sinusoidal) excitation field also helps in mixing the fluid more uniformly. This mixing action improves the overall accuracy of the measurement, especially for peripheral blood (e.g. finger stick blood) where tissue is a factor. To improve the mixing effect, the present invention can optionally be modified to include a commutated motor action or include rotating mixing magnets.
Increased viscosity and increased stress on the magnetostrictive particles also causes a change in the resonant frequency of the particles. By performing a sweeping operation over a frequency range with the driving current 7 into the excitation coil 6, the resonance can be located. As coagulation occurs, the frequency value of the resonant changes and can be tracked. The change in resonant frequency can be also nearly directly proportional to the viscosity of the fluid 2.
Once the test tube 1 or fluid container is placed in the housing 4, a proximity sensor can send a signal to a system level controller signifying the start of the process. This controller can then begin the process of measuring the viscosity by sending a command to the signal generator. The output signal from the signal generator can be fed to a power amplifier to cause drive current 7 to pass through the excitation coil 6. The sensing coil output voltage 9 can be processed through a signal-conditioning unit to clean up the signal and amplify it. The cleaned, amplified signal can then be fed into an optional zero adjustment circuit to maintain the desired sensitivity before reaching the system level controller.
The output of the sensing coil 8 may typically be an AC signal with a superimposed voltage change that is proportional to the change in viscosity or density. To maximize the sensitivity of the system, the sensing coil output signal 9 can first be rectified and then filtered followed by a zero adjustment. One way of achieving a zero adjustment is to subtract out the carrier signal. An adjustable zero reference provides an easy way to maximize the sensitivity of the sensor.
In the case of a frequency domain measurement (swept system), the change in resonance can be measured by a hardware circuit or it can be measured in software. Generally it is desirable to perform this resonance determination in real time. The choice of an amplitude or frequency method depends on the type of fluid and the sensitivity desired. Both methods are within the scope of the present invention.
It should be noted that the excitation and sensing coils can be arranged in many ways differently from what is shown in
The system can be fabricated conventionally or by using MEMS technology for cost and volume efficiency.
As an alternate to the embodiments presented thus far, reagents containing magnetostrictive materials can be deposited as layers of thicknesses of less than 0.1 micron to around 5 micron or greater on flat surfaces. An excitation coil(s) and a sensing coil(s) can be located external to the surface. The surface could be as simple as a throw-away slide. An embodiment of such a system is shown in
Various descriptions and illustrations have been presented to better aid in the understanding of the present invention. One skilled in the art would understand that many changes and variations are possible. The scope of the present invention includes these changes and variations.
This application is related to and claims priority from U.S. Provisional application 60/588,950 filed Jul. 19, 2004 and 60/511,565 filed Oct. 15, 2003. Application 60/588,950 and 60/511,565 are hereby incorporated by reference.
| Number | Date | Country | |
|---|---|---|---|
| 60588950 | Jul 2004 | US | |
| 60511565 | US |
