Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
  • A61B5/087—Measuring breath flow
  • A61B5/0876—Measuring breath flow using means deflected by the fluid stream, e.g. flaps

Definitions

• the present invention relates to resistive elements and air tubes for use with spirometers, and to spirometers using such resistive elements and air tubes. More particularly, the present invention relates to resistive elements and air tubes which are disposable and preferably at least partially biodegradable, to spirometers, preferably differential pressure spirometers, which employ such elements and tubes, and to calibration techniques for ensuring a high level of accuracy when the disposable air tubes are used with the spirometers.
• Spirometers are devices used to measure the volume and flow rate of gas exhaled and inhaled by a user or patient, for example, a human being.
• Two general types of spirometers measure volume and flow, respectively.
• the actual port of the spirometer used to measure flow is the pneumotach of which Fleisch is one type.
• These measurements are important for physiological studies and for diagnostic analysis of the pulmonary performance of the spirometer user. For example, the effects of various medicines used to treat patients with pulmonary or asthmatic problems can be analyzed by monitoring the volume and flow rate of gas exhaled before and after the administration of medication.
• pneumotachs such as the Fleisch Pneumotach. These devices depend on a laminar air flow past a resistance element. Other spirometers employ more sophisticated electronics so that laminar flow is not needed.
• Another approach to overcoming this contamination problem is to sterilize, in-between patients, the portion or portions of the spirometer which come in contact with the user and/or exhaled air.
• Drawbacks to this approach include having to spend additional capital on sterilization equipment and supplies, having to monitor the operation and efficacy of the sterilization equipment, and having to purchase relatively durable and expensive spirometers to withstand the sterilization procedures.
• a third alternative that has been suggested is the use of disposable spirometer components. See, for example, Norlien et al U.S. Patent 5,038,773; Acorn et al U.S. Patent 5,305,762; Karpowicz U.S. Patent Des. 272,184; Boehringer et al U.S. Patent 4,807,641; and Bieganski et al U.S. Patent 4,905,709.
• Such previous disposable spirometer components have generally been made out of durable plastics or medical grade metals so that, even though they are disposable, the cost of producing such components is relatively high.
• such disposable components are relatively difficult to dispose of, for example, because they are made of durable and long lasting materials.
• the economical manufacture of a relatively inexpensive spirometer component from a low cost and/ or biodegradable material has heretofore been prohibitive because of, for example, quality control concerns.
• General industry specifications require high quality spirometer components but the quality of these components can decrease as the components are made biodegradable, for example, placement of these components within the spirometer can also present problems.
• the placement of the resistive element within each air tube can affect the performance of the overall spirometer, for example.
• the resistive element is often placed in a normal or perpendicular configuration relative to the interior wall of the air tube and, further, should be placed at exact, predetermined distances from the two opposing ends of the air tube.
• Prior art resistive elements often do not exhibit linear resistance-versus-flow-rate responses.
• resistive elements configured to exhibit good resistance at high flow rates often do not perform adequately at low flow rates and, on the other hand, resistive elements configured to perform well at low flow rates often do not provide ideal resistance at high flow rates.
• any possibility of manufacturing a relatively inexpensive spirometer would appear to be vitiated due to manufacturing and performance concerns. These manufacturing concerns include the inconsistencies between various disposable, biodegradable spirometer components that may be produced on an assembly line and, further, include subsequent performance variances between the spirometer components resulting from these inconsistencies.
• Inconsistencies in these components may be augmented when they are assembled together or placed into the spirometer.
• a throughport of an air tube may not be perfectly formed, and the subsequent placement of this throughport onto the spirometer may introduce abnormally low pressure readings due to air leakage around the pressure port.
• Even placement of the resistive element within the air tube may not be exact between various assemblies and, accordingly, a problem of accuracy may even be prevalent among existing durable plastic or metal non-biodegradable components as well . Accordingly, it would be advantageous to provide a means of ensuring high performance quality and consistency between various spirometer components from an assembly line, regardless of whether the spirometer components are metal, plastic, or biodegradable.
• a typical resistive element for a spirometer includes a disk-shaped member with a large aperture through the center thereof.
• Other resistive elements of the prior art may include disk-shaped elements formed of a mesh material .
• Another prior art device includes a diamond-shaped window formed in a center portion of the disk shaped member. The diamond-shaped window is secured to a portion of the disk shaped element, and is adapted for opening and shutting to various extents or degrees, depending upon the air flow rate.
• a prior art resistive element formed of a mesh is typically rendered inoperative or inaccurate by moisture and sputom from the patient's breath, resulting in clogging of the mesh.
• Prior art resistive elements comprising a diamond-shaped window have been somewhat effective for low air flow rates, but have not provided fully effective resistance-versus-pressure responses at both high and low flow rates.
• New resistive elements and air tubes for use in spirometers and spirometers including such resistive elements and air tubes have been discovered.
• the present resistive elements and air tubes are disposable so that after use by a patient, they are removed from the spirometer and disposed of.
• the resistive elements and air tubes are almost completely biodegradable, can be manufactured relatively economically, and are capable of yielding high and consistent performance characteristics.
• biodegradable means that the component or material is decomposable into more environmentally acceptable components, such as carbon dioxide, water, methane and the like, by natural biological processes, such as microbial action, for example, if exposed to typical landfill conditions, in no more than five years, preferably no more than three years, and still more preferably no more than one year.
• the resistive elements and air tubes biodegradable provides substantial advantages.
• the resistive elements and air tubes are biodegradable, they can be made of materials which are inexpensive and plentiful (readily available) .
• the present resistive elements and air tubes are relatively inexpensive, easy and straightforward to produce. Subsequent calibration of the air tubes accounts for any discrepancies in size, shape, and performance of the air tubes.
• the present resistive elements and air tubes can be made economically, replacing a used air tube with a new air tube is done without substantial economic impact.
• the present resistive elements and air tubes can be replaced in the spirometer very easily.
• Spirometers employing the present air tubes, preferably calibrated air tubes provide cost effective, reliable and reproducible (from air tube to air tube) measurements of the pulmonary performance of the user, with reduced risk of contamination.
• the present disposable, biodegradable resistive elements and air tubes, preferably calibrated air tubes are inexpensive and easy to produce to acceptably precise specifications (for reproducible performance) , are effective and reliable in use, and are conveniently and effectively disposed of in an environmentally acceptable or safe manner to reduce the risks of contamination caused by spirometer use.
• the present invention is directed to air tubes for use in spirometers.
• the present air tubes comprise a tubular portion which defines an open inlet, an open, preferably opposing, outlet and a hollow space therebetween.
• the tubular portion is sized and adapted to be removably coupled to the housing of a spirometer.
• the air tube is disposable, i.e., can be removed or decoupled from the spirometer housing and disposed of without disposing of the housing.
• Substantially all of the tubular portion is preferably biodegradable.
• the open inlet is sized and adapted to be received in the mouth of the user of the spirometer.
• this open inlet and the area of the tubular portion near the open inlet act as a mouthpiece for the spirometer so that the user or patient using the spirometer can exhale into the air tube directly through the open inlet.
• No separate and/or specially configured (relatively expensive) mouthpiece/filter is needed when using the present air tubes.
• the present air tubes include a resistive element which is located in the hollow space of the tubular portion.
• This resistive element is sized to cause a pressure difference or differential as air flows in the hollow space across this element, and is adapted for providing an alinear flow-versus-pressure response. This response is subsequently linearized with software .
• the resistive element includes a planar portion having a first face and a second face, and a parameter connecting the first face to the second face.
• An aperture is formed in a center of the planar portion for connecting the first face to the second face.
• a plurality of slots in the planar portion extend radially from the aperture, thereby forming a plurality of hinged windows in the planar portion.
• Each of the slots includes a central end and a distal end.
• the resistive element further includes a plurality of hinge slots. Each hinge slot is connected to a distal end of a slot, and extends generally perpendicularly to an axis of the slot. A total number of hinge slots corresponds to
• the slots and hinge slots form arrowhead-shaped, hinged windows.
• Each hinged window includes a point, which points toward the center of the planar member, and a neck, which controls the flexibility of the window.
• a large neck reduces the flexibility of the hinged window, and a small neck increases the flexibility of the hinged window.
• the resistive element has an approximately linear pressure response over a range of flow rates from zero liters per second to 15 liters per second.
• an air tube is formed of a first tube, a second tube, and a collar tube.
• the first tube has a proximal end, a distal end, and a first diameter.
• the second tube similarly, has a proximal end, a distal end, and a second diameter that is approximately equal to the first diameter.
• a resistive element contacts the proximal end of the first tube and the distal end of the second tube, and has a third diameter that is approximately equal to the first diameter.
• a collar tube fits over both the proximal end of the first tube and the distal end of the second tube.
• the collar tube has an inner diameter that is approximately equal to the first diameter, and has an outer diameter that is larger than the first diameter.
• a through port is formed in the second tube.
• the through port opens directly into a hollow space defined by the tube assembly and is spaced from the resistive element.
• the through port provides communication between the hollow space of the tubular assembly and a pressure sensing assembly of a spirometer.
• the pressure sensing assembly of the spirometer compares a pressure from the hollow space with an atmospheric pressure.
• the tubular portions and resistive elements of the present air tubes preferably comprise biodegradable materials, and are more preferably 99% biodegradable.
• Preferred biodegradable materials of construction include cardboard, paper, biodegradable polymeric materials and the like and mixtures thereof.
• the tubular portion is made of cardboard or paper or mixtures thereof, more preferably produced by methods analogous to those conventionally used to produce tubes around which are wound bathroom tissue. Such production methods often include forming a cardboard or paper tube over a mandrel or a like implement and then cutting the resulting tube to the desired length.
• the tubular portion is made from a biodegradable polymeric material such tubes can be formed by conventional polymer molding techniques.
• the resistive element is placed relative to the tubular portion so that the pressure difference for any given rate of flow of air across the resistive element is the same from air tube to air tube.
• the resistive element is preferably located transverse to the longitudinal axis of the tubular portion.
• the resistive element can be placed in the tubular portion by adhering (for example, using biodegradable adhesives) the resistive element to the interior wall of the tubular portion or by joining two separate segments of the tubular portion together with the resistive element therebetween. Other methods or techniques for placing the resistive elements in the tubular portions may be employed.
• the resistive elements of the present air tubes designed for use in the same spirometer are structured and configured essentially the same, so that no recalibration of or other adjustment to the spirometer is needed because one air tube is replaced by another air tube.
• the present air tubes further comprise a positioning means or sub-system adapted to cooperate with the housing of the spirometer to properly position the air tube relative to the housing of the spirometer.
• a positioning means or sub-system adapted to cooperate with the housing of the spirometer to properly position the air tube relative to the housing of the spirometer.
• Any suitable positioning means may be employed to properly orient the air tube relative to the housing of the spirometer, for example, so that the through port of the air tube is properly aligned with the pressure sensing assembly of the spirometer.
• the positioning means includes a notch sized and adapted to cooperate with a projection on the housing of the spirometer.
• the positioning means includes a positioning port in the tubular portion sized and adapted to cooperate with a positioning projection in the housing of the spirometer. This is a particularly useful embodiment since the positioning port can be easily placed in the tubular portion of the air tube. Also, since the housing of the spirometer is often a molded polymeric component, the positioning projection can be easily formed in the spirometer housing.
• An air tube in accordance with the present invention can be snugly fitted into a hollow open space defined by a spirometer housing tube so that the through port of the tubular portion is properly aligned with the pressure sensing assembly of the spirometer.
• the projections of the housing can be placed in the notch of the tubular portion such that the through port of the tubular portion is properly aligned with the pressure-sensing assembly of the spirometer.
• a suction-cup shaped interface of the pressure sensing assembly fits snugly around the through port . The snugness of the fit between the air tube and the housing tube of the spirometer insures that the air tube can be used in conjunction with the spirometer without disturbing the through port/pressure sensing assembly alignment.
• the air tube can be relatively easily removed from the spirometer housing tube and replaced by a new air tube.
• the present air tubes can be designed and structured to be used with a retrofitted existing spirometer or with a spirometer specifically built for use with the air tubes. It is particularly useful to have the tubular portion longer than the housing of the spirometer so that in use the tubular portion extends beyond at least one end of the component of the housing of the spirometer to which the tubular portion is removably coupled. This feature is very attractive in preventing undue contamination of the spirometer housing by the user of the spirometer. Thus, the air which is exhaled by the patient passes through the tubular portion and does not come into significant or intimate contact with the housing of the spirometer.
• the present spirometers comprise a housing, an air tube as described herein, a pressure sensing assembly positioned relative to a through ports of the air tube to sense the pressure at the through port, and an electronic assembly coupled to the pressure sensing assembly for generating signals, preferably electrical signals, indicative of the differential between the pressure sensed at the through port and an atmospheric pressure.
• the electronic assembly can be disposed in the housing or can be located remote from the housing.
• the housing can be a hand held component which is connected, for example, by wire, cable, or an RF path, to an electronic processing system which includes a substantial portion of the electronic assembly of the present spirometer.
• the electronic assembly can be completely disposed in the spirometer housing so that a fully self-contained unit can be provided.
• Figure 1 is a side view of a spirometer in accordance with the present invention showing a portion of the electronics disposed apart from the hand held unit .
• Figure 1A is a front side view of the spirometer shown in Figure 1.
• Figure 2 is an exploded view of the air tube of the present invention
• Figure 3 is a cross-sectional view of the air tube of the present invention.
• Figure 4 is a top planar view of the resistive element of the present invention.
• Figure 5 is a partially cut away, top front view, in perspective, of the air tube used in the spirometer shown in Figure 1.
• Figure 6 is a somewhat schematic illustration showing a spirometer in accordance with the present invention.
• Figure 6A is a cross-sectional view taken generally along line 6A-6A of Figure 6.
• Figure 7 is a cross-sectional view taken generally along line 7-7 of Figure 1.
• Figure 8 is a side view of an alternative embodiment of a spirometer in accordance with the present invention.
• Figure 9 is a back side view of the spirometer shown in Figure 8.
• Figure 10 is a perspective view illustrating the bar code reading assembly of the spirometer of the presently preferred embodiment
• Figure 11 is a circuit diagram illustrating a specific implementation of the bar code reading assembly of Figure 10;
• Figure 12 is a schematic representation of a linear array of photodiodes for receiving light from a bar code label according to the presently preferred embodiment
• Figure 13 is a perspective view of a self focusing lens array used for focusing light onto the linear array of photodiodes, according to the presently preferred embodiment.
• Figures 14 and 15 illustrate perspective views of a spirometer design according to the presently preferred embodiment.
• a spirometer in accordance with the present invention shown generally at 10, includes a disposable, biodegradable air tube 12, a housing 14 and control electronics 16.
• Spirometer 10 is what is commonly known as a differential pressure spirometer and, in general, operates in a manner similar to the spirometer disclosed in the above-noted Waterson et al U.S. Patent 5,137, 026.
• the air tube 12 is described with reference to Figures 2 and 3.
• the air tube 12 includes a first tubular segment 18, a second tubular segment 20, and a collar tube 21.
• a resistive element 22 fits between the first tubular segment 18 and the second tubular segment 20.
• the air tube 12 and resistive element 22 are preferably approximately ninety-nine percent biodegradable.
• the tubular segments 18, 20, and 21 are made of biodegradable cardboard or heavy paper, for example, in a manner similar to how cardboard tubes are conventionally made, such as for use with bathroom tissue and the like products. These segments 18, 20, and 21 are preferably coated with a glossy layer.
• the resistive element 22 preferably comprises biodegradable material having good memory characteristics. As presently embodied, the resistive element 22 comprises a Nomex material.
• the resistive element 22 material may, alternatively, comprise any nylon or other material which is somewhat resistant to moisture . As presently embodied, the resistive element 22 is approximately .003 inches thick, but other thicknesses may be used according to design parameters .
• the resistive element 22 is first secured to either the first tubular segment 18 or the second tubular segment 20, and then the other tubular segment 18 or 20 is then secured to the resistive element 22.
• a biodegradable adhesive is preferably used.
• an outer diameter of the first tubular segment 18 is equal to an outer diameter of the second tubular segment 20, and the outer diameter of the resistive element 22 is equal to the outer diameter of the first tubular segment 18.
• An inner diameter of the collar tube 21 is approximately equal to the outer diameter of the first tubular segment 18.
• the collar tube 21 is adapted to fit over both the first tubular segment 18 and the second tubular segment 20.
• adhesives are preferably used for securing the resistive element 22 between the first tubular segment 18 and the second tubular segment 20
• the close, frictional fit of the collar tube 21 over the first tubular segment 18 and the second tubular segment 20 may be sufficient, alone, to secure the resistive element 22 between the first tubular segment 18 and the second tubular segment 20.
• the distal end 23 of the collar tube 21 is flush with the distal end 25 of the first tubular segment 18, when the collar tube 21 is properly secured over both the first tubular segment 18 and the second tubular segment 20.
• a notch 27, which preferably comprises a punched out semicircle in the distal end 23 of the collar tube 21, is preferably lined up with a port 24 of the second tubular segment.
• the port 24 of the second tubular segment 20 preferably comprises a punched out circle in the second tubular segment 20.
• the notch 27 and/or the port 24 may be formed in the collar tube 21 and/or the second tubular segment 20 either before or after assembly of the three pieces 18, 20, and 21. After assembly of the three elements 18, 20, and 21.
• the port 24 opens directly into a hollow space ( Figure 3) of the air tube 12.
• Figure 3 illustrates the air tube 12 in an assembled state. Although a three piece configuration of the air tube 12 is presently preferred, these three pieces 18, 20, and 21 may be replaced by a single tube, for example, and/or the resistive element 22 may be secured to an annular ring (not shown) , which is inserted within the single tube.
• FIG. 4 illustrates a top planar view of the resistive element 22, according to the presently preferred embodiment.
• the resistive element 22 comprises a center aperture 32 and a plurality of slots 34 extending radially from the center aperture 32.
• Each pair of adjacent slots 34 forms a hinged window 36, which as presently embodied comprises an arrowhead shape.
• Each arrowhead-shaped hinged window 36 comprises a point located near the center aperture 32 and a neck 38 located distally of the center aperture 32.
• the resistive element 22 comprises eight hinged windows 36, but greater or fewer numbers of hinged windows 36 may be used according to design parameters.
• the width of each neck 38 controls the flexibility of the corresponding hinged window 36. A larger neck renders the corresponding hinged window 36 less flexible, and a smaller neck 38 renders the corresponding hinged window 36 more flexible.
• a human patient blowing into an end of the air tube 12 generates an air flow through the resistive element 22 which, typically, may comprises an air flow rate of between zero and 16 liters per second.
• the resistance provided by the resistive element 22 should, ideally, be approximately linear among these various air flow rates.
• Prior art resistive elements, comprising a disk with a single aperture therein, for example do not have linear pressure versus flow rate relationships.
• the resistive element 22 of the present invention utilizes unique hinged windows 36 having necks 38, which can be engineered to tailor the resistance of the resistive element 22 at various flow rates.
• the resistive element 22 of the present invention is adapted to provide an ideal resistance of less than 1.5 centimeters of water per liter per second at a flow rate of approximately 12 liters per second but, in contrast to a conventional disk shaped resistive element, the resistive element 22 of the present invention also provides good resistance at low flow rates.
• the resistive element 22 provides a very good, approximately linear flow-rate- versus-resistance response for flow rates between zero and 16 liters per second.
• the hinged windows 36 open widely to provide a good resistance that is not too high.
• the hinged windows 36 open very little, to thereby provide a good resistance that is not too low.
• an angle between two of the slots 34 is approximately 45 degrees, and each of the slots 34 has a width of approximately .02 inches.
• a preferred width of each of the perpendicular hinged portions 37, which is used to control the width of a neck 38, is approximately .04 inches.
• the diameter of the resistive element 22 is preferably 1.09 inches plus or minus .0005 inches, and a width between a line 39 bisecting one of the hinged windows 36, and another line 41 passing through a slot 34 is approximately .0625 inches plus or minus .005 inches .
• resistive element 22 of the present invention is the resistance supplied at low flow rates, since, typically, unhealthy patients are unable to generate high flow rates .
• the same resistive element also functions well at high flow rates.
• the resistive element 22 provides good resistance at various flow rates, regardless of whether the patient is exhaling or inhaling.
• air tube 12 includes an open inlet 46 and an open outlet 48.
• the area surrounding the open inlet 46 is sized and adapted to be fitted into a human being's mouth.
• This mouthpiece area is employed by the patient using spirometer 10 ( Figure 1) by placing the area 46 into the mouth and exhaling into hollow space 30 of the air tube 12.
• spirometer 10 Figure 1
• the air tube 12 is coupled to the housing tube 51.
• the housing tube 51 includes a tab 52, which is adapted to fit within the notch 27 ( Figure 2) of the air tube 12.
• the notch 27 is aligned with the port 24 ( Figure 2) and, as presently embodied, is manually aligned by the user just before insertion into the housing tube 51.
• the port 24 will align with the pressure sensing leg 76, as shown in Figure 6.
• a fitting of the pressure sensing leg 76 which preferably comprises a suction cup shape 77 which fits around the port 24 for an airtight fit.
• the suction cup shaped fitting 77 preferably comprises silicone rubber or vinyl, and is adapted to provide a good fit around the port 24, to thereby attenuate any leakage of air at this interface. Consequently, breath from the patient is not introduced into the pressure sensing leg 76 and contamination of the pressure sensing leg 76 is avoided.
• FIG. 1 illustrates the general operation of a spirometer, shown generally at 10. The following is a general description of the operation of the spirometer 10 after the air tube 12 is properly located and positioned relative to the pressure sensing leg 76.
• the pressure transducer 80 generates an electrical signal on a pair of output wires 82 and 84, which signal is proportional to the differential pressure between pressure sensing leg 76 and a sensed atmosphere pressure. This signal is amplified by a differential amplifier stage 86 and fed into an analog-to-digital convertor 88 which converts the amplifier output into digital signals.
• the output from convertor 88 is fed to a microprocessor 90, which is part of control electronics 16.
• the microprocessor 90 uses calibration data supplied by coded information on the air tube 12 in combination with an algorithm stored in a ROM 92 to perform several calculations on the signal from convertor 88, and to display the calibrated final results, e.g., volume and flow rate, on display 94, for example, a conventional monitor or liquid crystal display module.
• Microprocessor 90 is powered by a power source 91, for example, either a battery or a connector capable of being coupled or connected to a source of conventional electric line voltage.
• Switch 96 can be activated to initiate the operation of the spirometer through microprocessor 90.
• the results during each measurement may be stored in a RAM 98 for future reference.
• An input/output port 100 may also be provided to allow for changing the programming of the microprocessor 90.
• the microprocessor 90 may be programmed so that on command it may download the results accumulated in RAM 98 through input/output port 100 to a printer or a computer.
• Waterson et al U.S. Patent 5,137,026 provides further details regarding the operation of a conventional spirometer.
• the biodegradable air tube 12 is removed from the housing tube and is disposed of in an environmentally safe manner.
• the housing 14 is structured to be gripped in one hand of the user.
• the shaft 102 of housing 14 is configured for easy hand gripping.
• finger indents 104 are provided to make hand holding this device even easier.
• the embodiment shown in Figures 1 and 1A includes control electronics 16 located within the hand held housing 14. Communication with external computers or printers can occur through cable 106 which can be connected to the convertor using a jack 105, such as a conventional RJ-11 quick connect jack, on housing 14. As presently preferred, communication can also occur through an additional infrared data association (IRDA) link, which is conventional, and operable between the housing 14 and the external computer or printer.
• IRDA infrared data association
• the electronics in the housing 14 are preferably powered by a battery pack, such as a conventional rechargeable nickel-cadmium battery. If such a battery pack is used, the housing 14 includes a port through which the battery pack can be charged.
• microprocessor 90 can be a dedicated microprocessor including a transparent-overlay keypad structured and adapted specifically to control the operation of a spirometer.
• the microprocessor 90 may be a component of a general purpose, personal computer including a full-sized keyboard, video monitor, hard disk drive and printer.
• the dedicated microprocessor is particularly advantageous because of its relative simplicity, reduced cost and ease of use.
• the shaft 102 of housing 14 includes a tapered portion 107, as shown in Figure 1A, which facilitates placing and maintaining the housing on a flat surface, for example, between uses.
• an existing spirometer includes a hand held unit including a permanent breathing tube, pressure sensing leg, a pressure transducer, an amplifier and an analog-to-digital convertor, and is connected to a dedicated control system, which functions in a manner substantially similar to control electronics 16.
• a retrofitted spirometer is produced which has many of the advantages of the present invention.
• Figure 7 shows a cross-sectional view of the spirometer 10 of Figure 1, taken along line 7-7 of Figure 1.
• FIG. 8 Another embodiment is illustrated in Figures 8 and 9.
• This spirometer, shown generally at 210 is, except as expressly stated herein, structured in a manner similar to spirometer 10.
• Components of spirometer 210 which correspond to components of spirometer 10 have corresponding reference numerals increased by 200.
• the primary differences between spirometer 210 and spirometer 10 have to do with the configuration of air tube 212 and the configuration of the housing tube 251.
• Air tube 212 is structured substantially similar to air tube 12 except that in the region near open outlet 248, two positioning ports 107 and 108 are provided.
• Housing tube 251 is structured to act as a cradle for air tube 212 rather than surrounding the air tube 212, as does housing tube 51.
• housing tube 251 includes two upwardly extending projections 109 and 110 which are positioned to be received by positioning ports 107 and 108, respectively, when air tube 212 is coupled to housing tube 251. With projections 109 and 110 mated to or received by positioning ports 107 and 108, the port 224 (not shown) is properly aligned with the pressure sensing leg 276 (not shown) .
• a transparent-overlay control keypad 112 of microprocessor 90 is located on the shaft 302 of housing 214.
• this embodiment preferably comprises greater ROM, and the display 94 is located on the housing 214 beneath the transparent-overlay keypad 112.
• the power source 91 is a battery pack, such as a conventional rechargeable nickel-cadmium battery, and is located within housing 214.
• Port 114 on housing 214 is adapted to provide communication between battery pack 91 and a conventional battery charger to recharge the battery pack when needed.
• I/O port 100 is also carried by housing 214 and provides convenient communication between microprocessor 90 and a computer or printer, when it is desired to download information from electronic circuitry 111 to such other device.
• an IRDA optical port is also disposed on the shaft 302.
• Spirometer 210 is a self-contained unit that can be operated by a single patient .
• air tube 212 is coupled to housing tube 251 so that projections 109 and 110 mate with positioning ports 107 and 108, respectively.
• the patient then activates a switch on the transparent-overlay keypad 112 and uses spirometer 210 for any treatment and/or diagnostic procedure desired.
• the biodegradable air tube 212 is simply picked up from the housing tube 212 and can be discarded in an environmentally acceptable manner.
• a character recognition unit 304 is disposed within the housing 14 of the spirometer 10.
• the character recognition unit 304 preferably comprises a device for recognizing bar ⁇ code-like stripes.
• the character recognition unit 304 is disposed within the housing 14 to align with a character sequence 306, preferably bar-code-like stripes, on the air tube 12, when the air tube 12 is placed within the housing 14.
• calibration information relating to the air tube 12 is coded within the character sequence 306. This coded information is read by the character recognition unit 304 and is conveyed to the converter 88 via line 308 and then to the microprocessor 90.
• the converter 88 preferably comprises eight inputs.
• the character recognition unit 304 is disposed within the housing 14 of the spirometer 10 to automatically read the character sequence 306, but, alternatively, this reading of information from the character sequence 306 may be performed manually. Human- readable characters may be disposed next to the character sequence 306, for example. Additionally, the reading of information from the character sequence 306 may be performed before, during, or after each reading by the spirometer 10, according to design preference.
• the character recognition unit 304 is preferably an optical character recognition unit, adapted for reading a bar code character sequence 306 but, alternatively, other information conveying techniques may be implemented.
• the character recognition unit 304 comprises a linear array for recognizing bar-type codes.
• Figure 6A illustrates a cross sectional view taken along line 6A-6A of Figure 6.
• a light source 310 projects light in the direction of the arrow Al onto a character sequence 306 disposed on a surface of the air tube 12.
• the character sequence 306 comprises a bar code label or, alternatively, a bar code printed directly onto the air tube 12.
• the light from the light source 310 reflects from the character sequence 306 in a direction of the arrow A2 and enters a self focusing lens array 313.
• a wedge shaped black plastic holder 318 is disposed between the light source 310, and the self focusing lens array 313, and the linear array of photodiodes 315.
• the wedge shaped black plastic holder 318 is adapted for securing these three elements 310, 313, and 315 thereto for proper alignment within the housing 14 of the spirometer 10.
• a perspective view of the character recognition unit 304 of the presently preferred embodiment is illustrated in Figure 10. Light from the light source 310 is focused onto the character sequence 306 disposed on the air tube 12.
• Reflective light is received by the self focusing lens array 313, which, as presently embodied, is disposed at an angle 321 of approximately 45 degrees from the light source 310.
• Both the light source 310 and the self focusing lens array 313 have lengths which are substantially parallel to a center line scan 323 passing through the character sequence 306.
• the linear array of photodiodes 315 is disposed substantially parallel to the self focusing lens array 313, and is adapted for receiving focused light from the self focusing lens array 313.
• An extraneous light stop 325 is disposed over a portion of the self focusing lens array 313, and another extraneous light stop 327 is disposed over the linear array of photodiodes 315.
• Figure 13 illustrates the clip-on light stop 325 adapted for accommodating the self-focusing lens array 313, according to the presently preferred embodiment.
• the light stop 325 preferably comprises black plastic, and may be frictionally fit around the self-focusing lens array 313 and/or secured thereto using an adhesive. Alternatively, less expensive light stop techniques may be implemented, according to design preference.
• both the light source 310 and the self focusing lens array 313 and, more preferably, also the linear array of photodiodes 315 are disposed on a wedge shaped black plastic holder 318.
• the wedge shaped black plastic holder 318 provides the correct angle between the light source 310, and the self focusing lens array 313 and the linear array of photodiodes 315.
• the wedge shaped black plastic holder 318 further facilitates proper spacing of the light source 310, the self focusing lens array 313, and the linear array of photodiodes 315 from each other and from the air tube 12.
• the wedge shaped black plastic holder preferably comprises a black color for suppressing light reflections.
• the total conjugate focal length 333 of the self focusing lens array 313 is preferably approximately 9.4 millimeters, measured from an internal sensitive surface of the linear array of photodiodes 315 to the target surface of the character sequence 306.
• the self focusing lens array 313 comprises a Selfoc® lens array, manufactured by Nippon Sheet Glass Co., Ltd.
• This self focusing lens array 313 is positioned midway between the linear array of photodiodes 315 and the character sequence 306 so that both the linear array of photodiodes 315 and the character sequence 306 are at focal points of the self focusing lens array 313.
• the self focusing lens array 313 is positioned 2.5 millimeters from the character sequence 306 and 2.5 millimeters from the linear array of photodiodes 315.
• An approximately 1 millimeter wide portion of the character sequence 306 image along the character sequence center line 323 is transferred by the self focusing lens array 313 to the linear array of photodiodes 315 when the character sequence 306 is illuminated by the light source 310.
• the self focusing lens array 313 is approximately 18 to 20 millimeters in length, and comprises a single row of lenses 336.
• the self focusing lens array 313 is preferably slightly longer than the linear array of photodiodes 315, which is approximately 16 millimeters in length, to insure that the entire linear array of photodiodes 315 receives an image, allowing for a plus or minus 1 millimeter misalignment and/or end lens damage on the self focusing lens array 313.
• the two focal points of an exemplary individual lens 336 of the self focusing lens array 313, which are not to scale, are shown at 339 and 340.
• the linear array of photodiodes 315 preferably comprises an intelligent optical sensor manufactured by Texas Instruments, model number TSL215, and comprising an array of 128 charge-mode pixels in a 128 X 1 linear array.
• the linear array of photodiodes 315 is preferred over a charge coupled device (CCD) because of ease of use, among other reasons.
• the linear array of photodiodes 315 comprises integrated clock generators, analog output buffers, and sample and hold circuitry that would otherwise be required by a CCD circuit.
• the focal point 340 for example, is focused approximately 1 millimeter beneath the top surface of the linear array of photodiodes 315.
• a clear plastic packaging 344 is disposed over the sensitive surface 346, as illustrated in Figure 12.
• the center scan line 323 is projected onto the sensitive surface 346, as shown by the line 348.
• the focal point 340 ( Figure 10) is approximately 1 millimeter beneath the top surface of the clear plastic packaging 344, and is projected onto the sensitive surface 346 of the array.
• the microprocessor 90 activates the light source 310 using the "illumination- on" signal line 350, which is connected to a parallel port pin 352 of the microprocessor 90.
• the light source 310 comprises a four element light emitting diode array of approximately 45 millicandelas
• the light source 310 (lumens/ster) , having a wavelength of approximately 635 nanometers and being approximately a lambertian source.
• the light source 310 is biased with a 20 milliamps of current on the middle two lamps and 25 milliamps of current on the end lamps, to provide an even illumination along the character sequence 306, according to the present invention.
• the light source 310 provides approximately 23 microwatts per square centimeter of illumination, and is positioned approximately 7 millimeters from the target bar code, as illustrated by reference numeral 354.
• the light stop 325 between the light source 310 and the self focusing lens array 313 suppresses stray light.
• the present invention incorporates a 635 nanometer wave length to roughly match the sensor peak responsivity of the linear array of photodiodes 315 which is approximately 750 nanometers.
• the sensitivity obtained in the linear array of photodiodes 315 is approximately 80% of the 100% maximum linear array sensitivity at 750 nanometers wave length.
• the light source 310 has a length of approximately 16 millimeters. As presently embodied, the light source 310 is only activated by the microprocessor 90 during bar code reads, since, obviously, activation of the light source 310 dissipates power.
• Both the light source 310 and the linear array of photodiodes 315 preferably comprise integrated circuits that are mounted on a flexible PC board, and form a dihedral angle 321 with respect to each other of 45%.
• the image integration time of the linear array of photodiodes 315 begins with a short pulse on line 360 by the microprocessor 90 into the serial input pin 362 of the linear array of photodiodes 315. After approximately 1 to 10 milliseconds, a second serial input pulse is input into the linear array of photodiodes 315 on line 360. After this second serial input pulse, the image is read on the video output pin 364 by clocking the clock pin 366 at between 10 kilohertz and 100 kilohertz, using 129 or more clock pulses . The resulting signal is placed on the serial video output line 368.
• the serial video output which comprises an analog voltage
• the analog to digital converter 370 which preferably comprises 12 bit accuracy and a 0 to 5 volt input range.
• the analog to digital converter 370 outputs digital data on data bus 373, which reflects the amplitude of each video pulse and, consequently, the darkness of each sensor pixel of the linear array of photodiodes 315.
• This digital data on data bus 373 is subsequently read by the microprocessor 90.
• the analog to digital converter 370 is controlled by the microprocessor 90, and has a conversion time of approximately 10 microseconds. Accordingly, the linear array of photodiodes 315 can be clocked at up to 10 microseconds (100 kilohertz) .
• the linear array of photodiodes 315 is powered by a 3 terminal voltage regulator 375 to maintain power supply noise and video array noise at a minimum.
• the Texas Instruments TSL215 is presently preferred, a newer Texas Instruments product, the TSL1402 may be used instead.
• This later model comprises twice an many pixels in the same length of 16 millimeters. The model has twice the resolution and will allow for more digits and more reliability. This later model is pin compatible, so that the number of clock cycles can simply be changed from 129 to 257, and is less susceptible to optical saturation.
• the TSL1402 further does not require the 40 millisecond initial pixel charge period, and would provide double the speed and accuracy.
• the character sequence 306 preferably comprises a bar code having either an Interleaved 2 of 5 ITF sequence, providing approximately 3 decimal digits of calibration data plus a check sum digit or, alternatively, may comprise a straight binary code.
• the straight binary bar code is presently preferred, and is configured to provide approximately five and one half digits plus a binary check sum of about six bits.
• the binary code will be NRZ (non-return-to-zero) with constant width bars and spaces, plus a starting mark. This configuration ensures that the total width of the code is constant and allows 1 millimeter on each side for code positioning error.
• the minimum white and black bar widths in the bar code are selected to be at least 2 to 3 pixels wide on the linear array of photodiodes 315.
• the minimum bar width is approximately twice that width. This configuration ensures that at least one pixel position in the video output 368 of the linear array of photodiodes 315 will go fully low or high, since one pixel in the array 315 is fully black or white, and not positioned half way between a black bar and a white area.
• the full high or low voltage, in relation to other voltages in the video output 368 of the linear array of photodiodes 315, is decoded by software to positively indicate a bar position.
• the light source 310 is preferably of constant intensity, variances in light source intensity between units and over time are compensated for by the present invention. For this reason, and to compensate for sensor efficiency, the light integration of the linear array of photodiodes 315 is adjusted.
• the level of the image video read from the linear array of photodiodes 315 can be increased by increasing the time between the serial input pulses on line 360, i.e., the time of light integration interval.
• the integration time is adjusted up until the amplitude is sufficient to detect white to black differences.
• the overall amplitude of the whole serial video data stream from each read operation forms a nonlinear curve, due to changes in light intensity along the light source.
• a running differential average or other indicator indicates the approximate white to black threshold along the entire video data length. This average will be used to detect white from black data by software comparison. High frequency noise is filtered out by software, and the resulting data stream comprises an image of the bar code. As presently embodied, this resulting data stream is decoded by the NRZ binary method or the interleaved 2 of 5 method, depending on the code used. This NRZ format changes the bar code color if the data bits do not change and does not change the bar code color when the bits do change.
• the resulting steam after being decoded by either the NRZ binary method or the integrated 2 of 5 method, comprises the original binary or decimal number that was originally encoded onto the air tube 12. This number is then used to calibrate this spirometric flow sensor.
• the linear array of photodiodes 315 must initially be preconditioned by a 40 millisecond operation period, before each bar code read, to thereby allow for each of the 128 pixels to change from white to black or vice versa, correctly. During this preconditioning period, the light source remains on, and the data from the bar code is ignored. Subsequently, several bar code scans are performed until the correct data is obtained, judging by the check sum embedded in the bar code. According, the total read operation is approximately 40 milliseconds plus 5 milliseconds per bar code scan, or about 100 milliseconds. Each bar scan requires 128 times 10 microseconds minimum time, or 128 times 100 microseconds maximum time. The time is determined by the required integration time, as mentioned above.
• the light source 310 is turned on continually during all bar code scans, up to 100 milliseconds, and is not turned off between individual 5 millisecond scans, since the pixels have to be illuminated throughout the integration time.
• An embedded microprocessor 16 bit timer is programmed to develop 10 to 100 milliseconds repeated time periods, with each period generating an interrupt .
• a timer interrupt starts a routine that outputs the integration start pulse if needed, and then outputs 129 clock pulses, timed by the timer.
• the analog to digital converter 370 is read by the microprocessor 90 via data bus 373 and stored for later analysis.
• the timer is stopped and the data is analyzed by the microprocessor 90 to find the moving white-black threshold level, for each pixel, using continuous filtering and averaging.
• the data is then filtered in software and compared to the moving threshold level, before being converted into bar codes.
• approximately 8 bar code scans are taken and stored at a time, requiring 8 times 12.5 milliseconds, or 100 milliseconds maximum time, so that the 40 milliseconds initial pixel charge time does not have to be repeated.
• this assembly may have to be adjusted to focus exactly on the character sequence 306 within plus or minus .3 millimeters, unless this is guaranteed by the manufacturing process.
• the focal distance may have to be adjusted in a low light environment, while a diagnostic program runs on the microprocessor 90 and continually scans the character sequence 306, outputing the percentage of read errors from reading the character sequence 306. This focal distance is preferably adjusted until the errors are minimized. Worst case or random bar code examples would preferably be used for this procedure.
• the testing procedure comprises subjecting each flow tube 12 to an air stream of 7.5 liters per second in the expiratory direction.
• a sensor leg similar to that shown in Figure 6 at 76, is placed over the through port 24 ( Figure 2) of the air tube 12, and this sensing leg is connected to a high-accuracy pressure sensor.
• a mechanical resonance filter may be required in the tube.
• the measured pressure in response to the air stream of 7.5 liters per second in the expiratory direction, is noted for each tube and, subsequently, a similar measured pressure for the same air flow rate in the inspiratory direction is obtained for each air tube 12.
• the present invention recognizes that, although manufacturing differences exist between each air tube 12, the pressure output versus airflow input curve for each air tube 12 is remarkably similar. More particularly, this pressure output versus air flow input curve for each flow tube 12 can be mathematically modeled by a third order polynomial with fixed coefficients. The polynomial for each air tube 12 varies by only a single gain factor.
• the response of any subject air tube may be calibrated to replicate an ideal or model response by merely multiplying the response of the subject air tube by a constant.
• the measured pressure of a subject air tube 12 can be compensated to achieve an ideal pressure output, for any given air flow rate between 0 and 16 liters per second.
• the present invention is described in a particular embodiment where calibration of each subject air tube can be performed by merely generating a single calibration constant for each air flow direction (inspiratory and expiratory) , the present invention is not limited to this exemplary embodiment.
• the model pressure measurements are obtained by averaging pressure measurements of a large initial sample lot of flow tubes 12 from the manufacturing line, as presently preferred.
• a gain factor is determined, based upon the tube pressure measurement of the subject air tube 12 and the tube model pressure measurements. For example, if the model pressure measurement for the inspiratory direction is slightly higher than the subject tube pressure measurement for the inspiratory direction, a correction factor is generated to increase the pressure measurement of the subject tube 12 to the model pressure measurement. This correction factor comprises a constant in the presently preferred embodiment .
• a look-up table having a number of subject-air-tube 12 measurements and corresponding correction factors may be used, as just one example.
• a look-up table may comprise a large number of subject tube pressure measurements according to desired accuracy, and corresponding correction factors.
• the correction factors calibrate each subject tube to a desired accuracy level.
• a single binary number is used to represent both correction factors for any subject air tube 12. Since the subject air tube 12 is tested for a measured pressure in both the inspiratory direction and the expiratory direction, two different correction factors will be generated, corresponding to the two measured pressure rates of the subject air tube 12.
• the single binary number is presently preferred to represent these two correction factors in a compressed form, and may also be obtained from a look-up table.
• FIGS 14 and 15 illustrate perspective views of a spirometer design according to the presently preferred embodiment.
• the air tube 212 is substantially covered by the housing, and the display 94 and transparent-overlay keypad 112 are larger than in previously described embodiments.

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• 1997
  • 1997-06-09 NZ NZ333263A patent/NZ333263A/xx unknown
  • 1997-06-09 CN CN 97197370 patent/CN1228015A/zh active Pending
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  • 1997-06-09 AU AU34811/97A patent/AU732670B2/en not_active Ceased
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