Patent Abstract:
Systems and methods for measuring the flow of a liquid along a conduit are disclosed. A heat source applies thermal energy to a portion of a liquid flowing along a conduit thereby elevating its temperature. A light source generates a first beam that passes through the liquid in the conduit downstream from the position of application of the thermal energy and an optical detector receives this beam in combination with a second beam that is not passed through the liquid in the conduit and measures a change in intensity of a combined beam. The time required for the heated portion of the liquid to move from the point of application of thermal energy to the point at which the beam passes through the liquid is measured. This measured time, along with the distance of separation of the heat source and the optical sensing means permits calculation of the velocity of the liquid in the conduit.

Full Description:
This application claims priority to application Ser. No. 10/146,588 filed May 15, 2002, now U.S. Pat. No. 6,932,796 as a continuation application thereof, the contents of which are incorporated by reference herein in its entirety. This application claims subject matter disclosed in application Ser. No. 09/867,003 filed May 29, 2001, now U.S. Pat. No. 6,582,393, the contents of which are incorporated by reference herein in its entirety. 

   BACKGROUND OF THE INVENTION 
   A. Field of the Invention 
   This invention relates to the measurement of properties of liquids moving in a conduit and specifically the measurement of the flow rate of a liquid moving at a relatively low flow rate of less than one liter per minute in a conduit. Most specifically, it relates to the measurement of the rate of infusion of therapeutic agents to patients to achieve highly accurate dosing of these patients according to a prescribed administration regimen. 
   B. Related Art 
   Many methods of measuring the flow rate of liquids, and in particular the rate of infusion of a pharmaceutical to a patient are known. Best known are positive displacement systems wherein a known volume of fluid is moved over time independent of other system parameters such as pressure and liquid viscosity. Today, the most commonly used positive displacement pump for accurate infusion of a pharmaceutical to a patient is the syringe pump. A motor moves a plunger down the barrel of a syringe with tightly controlled manufacturing tolerances on inside diameter. The rate of advance of the plunger times the time of advance times the cross-sectional area of the syringe determines the volume of fluid infused. This positive displacement method is used, for example, in the MiniMed Model 508 insulin pump, the current market share leader in insulin pumps. The suggested retail price for the MiniMed 508 pump is $5,995.00. 
   A second example of a positive displacement system is the peristaltic pump, where rollers placed against a flexible conduit roll along the conduit to move the fluid down the conduit. In peristaltic pumps, enough force is applied to the liquid in the flexible conduit to eliminate any dependence on pressure and viscosity. However, the volume of liquid dispensed remains dependent on the volume of fluid in the tubing, which depends on the square of the inside diameter of the elastomeric tubing. Since the manufacturing tolerance on the inside diameter of economic elastomeric tubing is on the order of +/−10%, the delivery accuracy is limited to +/−20%. Peristaltic pumps are also expensive, but somewhat less expensive that syringe pumps. Today, peristaltic pumps are seldom used for accurate delivery of pharmaceuticals. 
   Given the expense of these positive displacement pumps, and the need to find less expensive systems for accurate delivery of pharmaceuticals, many other devices and methods have been proposed to maintain the required level of accuracy while reducing the cost. It is clear that many of these proposed systems achieve the goal of reduced expense. However, the problem that these proposed schemes face is that they do not achieve the required accuracy of delivery of the pharmaceutical. For example, in a liquid dispensing system with a pressurized liquid container where the pressure on the liquid forces it along the conduit, the parameters dictating the flow include the pressure that is causing the liquid to flow, the inside diameter of the conduit along which the liquid is flowing, the length of the conduit, and the viscosity of the liquid, which is in turn dependent on the temperature of the liquid. This problem is further compounded by the fact that the dependence on the inside diameter of the conduit is a fourth power dependence. In many delivery systems of this type, the pressure on the liquid decreases as the amount of liquid in the container decreases, leading to a reduction in the flow rate. The solution to this pressure decrease is known. O&#39;Boyle in U.S. Pat. No. 4,874,386, teaches a liquid dispensing device that accurately controls the pressure in this type of dispensing system by incorporating a constant pressure spring. But the dimensions of the flow conduit, its cross section, and the temperature for viscosity control are left uncontrolled, with the result of inaccurate dispensing of the fluid. 
   In order to overcome the situation of having to manufacture dispensing system components to higher tolerances than is economically feasible, many methods of measuring the liquid flow rate have been taught. If the actual flow rate is measurable, the flow rate may be adjusted to the desired flow rate. Or, if an accurate total volume rather than flow rate is required, the required time of flow may be calculated using the actual flow rate to achieve the desired volume. 
   In general, the different types of liquid flow measuring systems can be divided into two classes—those that require contact with the liquid to measure the flow, and those that measure the flow without requiring contact with the liquid. Flow measuring systems in the first class include a) turbines, where the angular speed of the propeller in the stream is a measure of flow rate, b) pressure drop systems, where the pressure difference across a flow resistor is used to calculate the flow rate, and c) certain forms of “thermal time of flight” systems where elements that add heat to the stream and measure heat in the stream are used to measure flow rate. Examples of these “thermal time of flight” systems are taught by Miller, Jr. in U.S. Pat. No. 4,532,811 and by Jerman in U.S. Pat. No. 5,533,412. However, in many liquid delivery systems, the conduit along which the liquid flows requires frequent replacement and, in the case of pharmaceutical infusion systems, the total flow path must also be kept sterile. In this first class of types of flow meters, the added complexity of adding components, and their necessary leads and connectors to the replaceable conduits, causes the replacement conduits to be expensive. And if these additional components are added to a reusable portion of the dispensing system, the replacement of the liquid container, or addition of fresh liquid to an existing container opens the flow path to an unsterile environment. For these reasons, attention has been paid to the invention of the second class of flow meters—those that do not require contact with the liquid in the conduit and add complexity to the conduit. 
   Kerlin, Jr, in U.S. Pat. No. 4,777,368, teaches a method and apparatus for non-contact measurement of the velocity of a moving mass. In a preferred embodiment, an infrared heat source raises the temperature of an element of the moving mass and an infrared detector, viewing this element of the moving mass at a later time, detects the heated element and records the time required for the moving mass to move from heater to detector. Given the physical separation of the heater and the detector, the speed of the moving mass may be calculated. Kerlin makes reference to the use of this concept for liquids as well as solids. Goldberg, in U.S. Pat. No. 4,938,079 teaches the same basic concept as Kerlin, Jr. with the modification that microwave energy is used to heat the liquid within a conduit and a microwave detector is used to sense the heated liquid downstream from the heater. Frank et al in U.S. Pat. No. 5,211,626 also teaches a thermal time of flight flow metering method, and while at least one infrared detector is used to detect the heated liquid, the liquid is heated by thermal contact with the liquid through the wall of the conduit. Taught by Goldberg and Frank is the need for accurate delivery of the liquid (although Frank admits that his teachings apply only to relatively non-accurate delivery of the liquid) the need for a closed flow path, and the need for an inexpensive replaceable conduit. However, each of these patents fails to recognize that the measured time of flight and the calculated stream velocity are insufficient to completely correct for variations in system components. Flow rate, as measured in volume per unit time, requires not only a measurement of the time, but also the volume of liquid dispensed in that time. Or, if the measurement of velocity is made, as described in all three of these teachings, then to obtain the flow rate, the cross-sectional area of the conduit must be known. These above three teachings teach the measurement of time only. The volume component is critically dependent on the inside diameter of the conduit. If time is the measured parameter, then flow rate depends on the cross-sectional area of the column of liquid and the length of the column of liquid. The cross-sectional area depends on the square of the inside diameter of the conduit. As described above, typical tolerances on the inside diameter of a conduit, especially for conduits of relatively small inside diameter, are +/−10%. Hence the variation in volumetric flow rate, even given a perfectly accurate measurement of the time of flight, is +/−20%. And if the liquid velocity is calculated from the time of flight, the flow rate depends on the cross-sectional area, which, as described above, leads to a flow rate uncertainty of +/−20%. And in situations where the conduit is to be replaced frequently, unless the inside diameter of the conduit is measured by the device or measured in the factory and communicated to the device, both expensive steps, the uncertainty due to the unknown inside diameter remains. A device and method that achieves accurate measurement of flow rate, and hence accurate liquid delivery by compensating for both variations in the inside diameter of the conduit and the velocity of the liquid flowing in the conduit is disclosed in pending U.S. application Ser. No. 09/867,003 filed May 29, 2001. This application is incorporated herein by reference. 
   In the teachings of U.S. Pat. Nos. 4,777,368, 4,938,079, and 5,211,626 there are additional practical considerations that make these teachings difficult to reduce to practice in cost-effective commercial products. The first of these practical aspects is the heating of the portion of the liquid to be sensed. Due to the high heat capacity and the rapid thermal diffusivity of virtually all liquids of commercial importance, and especially water, which is the base of all pharmaceutical infusion fluids, heating the liquid fast enough and to a high enough temperature to realize an operation flow meter is very difficult. Kerlin, Jr. in U.S. Pat. No. 4,777,368 implicitly recognizes this by advocating a high power CO2 laser. Neither Frank in U.S. Pat. No. 5,211,626 nor Goldberg, in U.S. Pat. No. 4,938,368 recognize this problem. And the problem is especially acute for Frank since his teachings require the heat to pass through the wall of the conduit by conduction, which is especially time-consuming and lossy. A solution to this problem, which is not alluded to in any of these three teachings, is to stop the flow of the liquid and to heat the liquid while it is stationary. The flow rate is measured by restarting flow once the liquid is heated. The two advantages of stopping the flow to heat the liquid is that the total mass of liquid that must be heated is greatly reduced and the heat pulse is relatively confined in position along the conduit. This solution is taught in pending U.S. application Ser. No. 09/867,003. 
   The second practical aspect which makes the prior art teaching, including the teaching in pending U.S. application Ser. No. 09/867,003, difficult to commercialize is the mode of detecting the heat pulse. Many pharmaceutical solutions, especially protein solutions such as insulin, degrade at temperatures above room temperature, and begin to denature at temperatures above 40 deg centigrade. A preferred temperature rise would be less than 5 centigrade degrees above ambient. For these systems to operate successfully the heated portion of liquid must be accurately detected and its location along the conduit accurately measured. Detection methods relying on detecting the infrared radiation from such a small change in temperature, such as proposed by Frank in U.S. Pat. No. 5,211,626, Kerlin, Jr. in U.S. Pat. No. 4,938,079, and Sage, Jr. in pending U.S. application Ser. No. 09/867,003, must operate in the far infrared where detectors are either too slow to respond to the heated liquid or must be cooled, making them large, energy consuming and expensive. Goldberg in U.S. Pat. No. 4,938,079 is sensitive to this issue, but offers no data to support a practical or operational device. 
   Thus there continues to be a need for improved devices and methods for accurate and economical measurement of liquid flow in liquid dispensing systems, especially in the area of infusion of pharmaceutical solutions. This invention meets these needs. 
   An object of the current invention is to provide an accurate, inexpensive, and practical system and method for measuring the volumetric flow of a liquid in a conduit. 
   It is a further object of the current invention to use this system and method for measuring the volumetric flow of a liquid in a conduit to infuse pharmaceutical solutions. This flow rate may be used for either accurate delivery of the pharmaceutical solutions or, when zero flow rate is measured, to detect occlusions in a delivery system for pharmaceutical solutions. 
   It is yet another object of the current invention to provide an accurate, inexpensive and practical system and method for detecting and measuring the temperature of a liquid in a conduit. 
   SUMMARY OF THE INVENTION 
   The present invention provides for a device and method for measuring the time of flight and/or the velocity of a liquid moving in a conduit. The apparatus includes an optically transmissive conduit through which the liquid flows. A light source illuminates a portion of the liquid through the optically transmissive conduit. A portion of the illumination proceeds by reflection at the liquid conduit interface to a detector in one embodiment. A portion of the illumination proceeds by transmission through the conduit and liquid to a detector in a second embodiment. In a second embodiment, the light source is a coherent light source, and a second reference pathway is provided to the detector. 
   When a heated portion of the liquid, which has been heated upstream of the position of illumination of the liquid, flows through the illumination a property of the reflected or transmitted illumination changes due to the change of the index of refraction of the heated portion of the liquid. In the reflected illumination embodiment, the intensity of the reflected illumination changes. The detector detects this change. In the transmitted illumination embodiment, the phase of the transmitted illumination changes. The detector detects this change. The time required for the heated portion of the liquid to flow from the heating position to the detecting position is a measure of the time of flight of the liquid. When combined with the physical distance between the location of heating and the location of detection, this time of flight provides the velocity of the liquid. When combined with the cross sectional area of the conduit, provided the conduit is of uniform inside diameter, this liquid velocity provides the volumetric flow rate of the liquid. 
   Other aspects and advantages of the invention will become apparent from the following detailed description and drawings of two embodiments of the invention. 

   
     BRIEF DESCRIPTION OF THE DRAWINGS 
       FIG. 1  is a function block diagram of a liquid dispensing system with a flow meter designed according to the invention. 
       FIG. 2  is an optical schematic of the portion of the liquid flow meter where the change in the index of refraction is detected by measuring the change in the intensity of light reflected from the inside surface of the conduit. 
       FIG. 3  is a theoretical plot of the intensity of the light reflected from the inside surface of a glass conduit when water is flowing as a function of the angle of incidence of the light from a light source. 
       FIG. 4  is an optical schematic of the portion of the liquid flow meter where the change in the index of refraction of the liquid is detected by measuring the difference in phase difference between coherent light transmitted through the conduit and a reference light path. 
   

   DETAILED DESCRIPTION OF THE INVENTION 
   The optical flow meter of this invention will be described in terms of a liquid dispensing system for use in infusion of pharmaceutical solutions.  FIG. 1  shows a block diagram of such a system. The liquid to be dispensed is contained in pressurized reservoir  10 . When pinch tube member  14  is moved away from stop  12 , conduit  11  is opened and the liquid is free to flow down conduit  11  to the flow outlet. When pinch tube  14  presses conduit  11  against stop  12 , stopping flow, the liquid is not free to move down the conduit to the flow outlet. At a selected time, microprocessor  17  signals heating element  13  to heat the portion of the liquid at its location along the conduit. Once the portion of the liquid is heated, the pinch tube member is moved away from the conduit, and the liquid begins to flow. At some later time, the heated portion of the liquid passes heat sensor  16  where the heated portion is detected. The time required for the heated portion of the liquid to move from the location of the heater to the heat sensor is measured. Additionally, the velocity of the liquid may be calculated by dividing the distance between the heating element  13  and the heat sensor  16  by the measured elapsed time. 
   A first preferred embodiment of heat sensor  16  is shown in  FIG. 2 . Within heat sensor  16  is optical detector  30 . Conduit  11  of  FIG. 1  is shown in section with conduit wall  33  and conduit lumen  32 . Conduit wall  33  is optically transparent, made of any material capable of achieving optically smooth surfaces but preferably made of glass. Also preferably, conduit wall  33  has at least one flat side. One trivial example of conduit  11  is square or rectangular in cross section, as shown in  FIG. 4 . Prism  31  is in optical contact with conduit wall  33 . Prism  31  is preferably mounted on conduit wall  33  by optical cement but may be mounted on conduit wall  33  with an optical index matching medium or conduit  11  and prism  31  may be an integral structure. Optical prism  31  is also made of any optically transparent material capable of achieving optically smooth surfaces such as glass or polycarbonate. Preferable, the index of refraction of conduit  11  and prism  31  are matched at the wavelength of light from light source  36 . 
   Light from light source  36  follows path  35  and is preferably normally incident on the left surface of prism  31 . Light from light source  36  continues through the interface between prism  31  and the outside surface of conduit  11 , through conduit wall  33  to the interface between the inside wall of conduit  11  and the liquid in lumen  32  at point  39 . At this interface at point  39 , light is both reflected (beam  37 ) and refracted (beam  34 ). The reflected light beam  37  proceeds out of prism  31 , preferably normal to the right surface of prism  31  and proceeds to light detector  38 . The fraction of the intensity of light  35  that is reflected at point  39  to form light beam  37  may be calculated using the standard Fresnel equations. A graph of this calculation for all angles of incidence from normal incidence (where beam  35  would be normal to conduit outside surface  33 ) to the critical angle (where total internal reflection occurs) is shown in  FIG. 3 . The materials used for this calculation are BK-7 glass for prism  31  and conduit  11  and water for liquid  32 . Shown in this figure is the reflected energy for P polarization. The preferred embodiment utilizes P polarization for beam  35  because of the larger reflected signal. The light detector will typically be monitoring changes in reflectance, not absolute reflectance. As a consequence, it is more germane to calculate the change in the reflected light (beam  37 ) as a function of angle for a given change in temperature of the fluid. Solid curve  21  in  FIG. 3  shows the percentage change in the reflected light (beam  37 ) as a function of reflected angle for a change in fluid temperature of 10 centigrade degrees. As can be seen from the solid curve  21  in  FIG. 3 , there is a range of angles of incidence from about 45 degrees to nearly 60 degrees where the percent change in the reflected signal is relatively large (about one percent of the reflected intensity) and relatively independent of the angle of incidence. The intensity of the refracted light in light beam  34  is the difference between the incident intensity and the reflected intensity. This light is directed down the flow tube, away from light sensor  38 . 
   When light source  36  of  FIG. 2  emits steady illumination, and the temperature of liquid  32  remains constant, the intensity of light beam  37  is constant, and detector  38  detects no change in the intensity of light beam  37 . However, when the portion of liquid in lumen  32  that has been heated by heat source  13  in  FIG. 1  passes point  39 , the intensity of light beam  37  will change as a consequence of the dependence of the index of refraction of fluid  32  on temperature. For example, in the preferred embodiment, heated water has a lower index of refraction than cooler water, thus more light will reflect when water of a higher temperature is present at location  39 . In one specific embodiment, the incident/reflected angle is 60 degrees, the water temperature is 20 centigrade degrees prior to heating and 25 centigrade degrees after heating. In this specific embodiment, 10% of the incident light is reflected for water prior to heating as shown by the dashed curve in  FIG. 3 . Once heated water is present at location  39 , the signal will increase by 1%. Thus, one milliwatt illumination will present a constant signal of 100 microwatts to detector  38  via beam  37 . When heated water (25 centigrade degrees) is present at location  39 , the signal will increase to 101 microwatts. Given today&#39;s laser and detector components, generating and detecting these signals are routine. 
   Note that with the appropriate conduit  11 , it is possible to detect the presence of the heat pulse in liquid in lumen  32  by detecting a change in intensity in refracted light beam  34 . While this is a much larger base signal (approximately 90% of the intensity incident at point  39  is in light beam  34 ), the magnitude of the change in the intensity of light beam  34  due to the passing heat pulse in liquid  32  is equal to that received by detector  38  shown in  FIG. 2 . 
   The output from detector  38  in  FIG. 2  is an electronic signal that changes with the temperature of the heat pulse in liquid  32 . This electronic signal may be subjected to either analog or digital processing to measure the time of flight from the location of heat source  13 . By analog processing, the signal may be differentiated, and the axis crossing of the differentiated signal would be a measure of the location in time of the peak of the heat pulse in liquid  32 . The time of this axis crossing could be used to identify the time when the peak of the heat pulse passed location  39  in  FIG. 2 . This and alternate methods of processing an analog electronic signal to locate the heat pulse in time are known to those skilled in the art of analog signal processing. Alternately, the electronic signal from detector  38  could be processed digitally to locate the heat pulse in time. The center of gravity of this electronic signal could be calculated, and the location in time of this center of gravity could be used to measure the time required for the heat pulse to move from the heat source  13  to location  39  in  FIG. 2 . 
   A second preferred embodiment for heat sensor  16  in  FIG. 1  is an interferometric measurement of the index change induced by temperature in liquid  32 . A specific embodiment of this concept with a Michelson interferometer is shown schematically in  FIG. 4 . However, with the appropriate illumination, detection, and construction, other interferometer configurations are applicable. 
   Shown in  FIG. 4  is a specific embodiment of conduit  11 : a rectangular conduit  50  containing liquid in lumen  32 . Conduit  50  is optically transparent and manufactured from any material capable of achieving optically smooth surfaces on both the inside and outside surfaces of the top and bottom of conduit  50 . Optical glass is preferred, but certain optical polymers such as polycarbonate would also be acceptable. 
   Also shown in  FIG. 4  is coherent light source  100 . Light source  100  is preferably a laser, but any light source with the appropriate coherence length would be appropriate. Elements  102  and  104  are beamsplitting elements, preferably 50% transmissive and 50% reflective. Elements  101  and  103  are reflective mirrors. Element  175  is a detector suitable for detecting the emission of light source  100 . In one embodiment, element  150  is an optical path delay element (e.g. glass, polycarbonate, fiber loop, et. al.). In this embodiment, it is preferred that the delay element provides a precise delay of one half of the wavelength of illumination. In another embodiment, element  150  is a separate section of conduit  50  where the liquid in lumen  32  has not been heated. 
   Light beam  110  emanates from source  100 . This beam is split into two paths by beamsplitter  102 . One beam,  111  passes through conduit  50  and subsequently fluid the liquid in lumen  32 . Depending on the definition of element  150 , beam  112  may pass through air, an optical delay element, or a separate section of conduit  50 . Beam  111  is reflected by mirror  101  and redirected towards beamsplitter  104 . Beam  112  is reflected by mirror  103  and redirected towards beamsplitter  104 . Beam splitter  104  combines beams  111  and  112  into beam  113 . Beam  113  is now the coherent sum of the two beams,  111  and  112 . The phases of beams  111  and  112  add, creating an intensity pattern that is dependent upon the phase delay induced by the liquid in lumen  32 . This intensity pattern is detected by detector  175 . 
   When fluid  32  is heated, the index of refraction changes. As a consequence, so does the phase of beam  111 . This in turn causes an intensity variation that is detected by detector  175 . In the specific embodiment where element  150  produces an optical delay of precisely one half of a wavelength in beam  112  prior to heating the liquid in lumen  32 , the intensity detected by detector  175  will be very small. Then, when fluid  32  is heated, the percentage change in intensity at detector  175  will be very large. 
   The electrical signal may be processed in ways similar to the electrical signal described earlier for the first embodiment where the heat pulse is detected as a change in illumination reflected from point  39  in  FIG. 2 . 
   The descriptions of these two embodiments illustrate how a heated segment of a liquid in a conduit may be used to measure the flow of the liquid down the conduit, thereby providing information allowing the calculation of the velocity of the liquid in the conduit. In pharmaceutical applications, such measurements provide the basis for the more accurate delivery of the pharmaceutical solution. Also in pharmaceutical delivery applications, especially during intravenous administration when the conduit is part of an IV administration set and the motion of the liquid is caused by gravity or an infusion pump, there is also a need to verify that the liquid path stays open. Frequently, for example when a patient rolls over, the administration set may be crimped, stopping flow even though the infusion pump is operating or there is adequate head on the gravity flow system. The flow sensor of this invention is also capable of the rapid detection of this situation. Whenever such an occlusion of the conduit occurs, the heated segment of the liquid does not move when the pinch tube is opened. Hence the detector does not detect any change in an optical property of the illumination. The absence of a detected signal from the heated segment of the liquid is then a measure of lack of flow, which may be caused by an occlusion in the conduit or a number of other possibilities. Thus the flow sensor of this invention also provides for the detection of flow system failures, among which is an occluded conduit. 
   The descriptions of the optical systems of  FIGS. 2 and 4  are meant to be illustrative and not definitive. Persons skilled in the art may be able to provide variations on the basic design of these optical systems in the detecting and measuring a heat pulse in a liquid in a conduit and the subsequent measurement of the flow of the liquid in the conduit.

Technology Classification (CPC): 0