US3838682A - Automated blood analysis system - Google Patents

Automated blood analysis system Download PDF

Info

Publication number
US3838682A
US3838682A US00319561A US31956172A US3838682A US 3838682 A US3838682 A US 3838682A US 00319561 A US00319561 A US 00319561A US 31956172 A US31956172 A US 31956172A US 3838682 A US3838682 A US 3838682A
Authority
US
United States
Prior art keywords
blood
fluid
valve
catheter
withdrawal
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
US00319561A
Other languages
English (en)
Inventor
Justin S Clark
Lloyd George Veasy
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
PRIMARY CHILDRENS HOSPITAL
Original Assignee
PRIMARY CHILDRENS HOSPITAL
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by PRIMARY CHILDRENS HOSPITAL filed Critical PRIMARY CHILDRENS HOSPITAL
Priority to US00319561A priority Critical patent/US3838682A/en
Priority to FR7347049A priority patent/FR2212940A5/fr
Priority to JP744318A priority patent/JPS5649575B2/ja
Priority to DE2365048A priority patent/DE2365048A1/de
Priority to GB5974573A priority patent/GB1463675A/en
Priority to US490603A priority patent/US3910256A/en
Application granted granted Critical
Publication of US3838682A publication Critical patent/US3838682A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N35/00—Automatic analysis not limited to methods or materials provided for in any single one of groups G01N1/00 - G01N33/00; Handling materials therefor
    • G01N35/00584—Control arrangements for automatic analysers
    • G01N35/00594—Quality control, including calibration or testing of components of the analyser
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N35/00—Automatic analysis not limited to methods or materials provided for in any single one of groups G01N1/00 - G01N33/00; Handling materials therefor
    • G01N35/00584—Control arrangements for automatic analysers
    • G01N35/00594—Quality control, including calibration or testing of components of the analyser
    • G01N35/00693—Calibration

Definitions

  • ABSTRACT A system for automatically withdrawing blood from a patient and testing various parameters of the blood, such as oxygen saturation, hemoglobin, gas content (P PCO and pH, includes a withdrawal unit which automatically withdraws a measured volume of blood, and returns all of it to the patient except a small measured quantity which is provided to an analysis unit that measures the gas content and pH.
  • the withdrawal unit includes provision for continuously monitoring patients blood pressure, irrigation from a standard I. V. source between blood withdrawals, or a constant low flush of saline, alternatively, as well as detection of any air in the blood, which results in shutting down the system and activating an air alarm.
  • the withdrawal unit also has provision for automatically withdrawing a small sample of blood, measuring oxygen content, and returning all blood to the patient, all on a programmed basis.
  • the analysis unit includes two-point gas and pH calibration and includes use of calibration fluid for washout. In each complete use cycle, blood from the withdrawal unit is washed into the analysis unit and blood in the analysis unit is moved and washed out using saline, water and calibration fluids.
  • the withdrawal unit may be used alone to acquire blood samples, and the analysis unit may be fed by more than one withdrawal unit or by manuallyacquired blood specimens.
  • FIGQI (SYSTEM) 8 PSI SALINE -IIo SALINE JIGS I38 CONSTANT VOLUME 3 PUMP RESERVOIR (W FIG..2 (WITHDRAWAL UNIT) TO BLOOD CUP (FIG. 3)
  • FIG. 4 TIMING UNIT
  • FIG. 4 AUTOMATED BLOOD ANALYSIS SYSTEM The invention described herein was made in the course of work under a grant or award from the Department of Health, Education, and Welfare.
  • BACKGROUND 1 Field of Invention This invention relates to automated blood analysis systems, and more particularly to apparatus for automatically withdrawing and testing blood.
  • a principal object of the present invention is to provide improved blood analysis capability.
  • Another object of the invention is to provide in1- proved automatic blood withdrawal and analysis units.
  • a further object of the invention is provision of a blood withdrawal unit capable of automatic interspersion of blood withdrawal cycles with constant irrigation or flush cycles for use with a continuously indwelling catheter.
  • Still other objects of the invention include provision of blood apparatus with improved self cleaning. automatic calibration. shorter equilibration times. and with improved integrity of the test results.
  • an auto mated blood analysis system which requires very little blood, isolates hazardous blood testing units from the patient, is self-calibrating and self cleaning, and is capable of utilization with multiple automatically or manually derived blood specimens.
  • an automatic blood testing system having: a novel fluid reservoir; capability to return substantially all withdrawn blood to the patient; an analyzer which can be shifted between and used with any one of several blood withdrawal units; an analyzer/withdrawal arrangement where only the withdrawal unit requires sterilization and contamination of the withdrawal unit by the analyzer is precluded; a combination blood withdrawal/infusion unit where intravascular (I.V.) solution flow is continuous, i.e., to the patient during the infusion mode and to waste during blood withdrawal; initial calibration fluids which are used to displace blood within the blood testing system; a control arrangement based on sensing a blood/transparent fluid interface which moves within the system according to a program.
  • I.V. intravascular
  • an automated blood system adapted for connection with an indwelling catheter includes alternatively operable means for providing l.V. infusion, constant catheter flush, or blood withdrawal. without necessitating rearrangement of apparatus, by means of a novel and improved automated valving arrangement.
  • automatic blood analysis apparatus is provided with a plurality of sources of fluid, said fluid having a characteristic similar to a characteristic of blood which is to be tested, said apparatus including testing stations interconnected with said fluid sources by valve means programmed in a fashion to provide calibration of said test station prior to the testing of blood therewith and further calibration following the testing of blood therewith.
  • automated blood testing apparatus includes a gas test station and a pH test station, and valving means for applying blood first to said pH test station and then to both said pH test station and said gas test station, the fluid in said test stations being in electrical communication with one another, said apparatus providing a first test of blood at said pH test station at said first time and a second test at said pH station at said second time, a substantial variation in the results of said first and second tests being indicative of a fault at said gas test station.
  • washout water used to cleanse a test station is provided with a measure of a substance for which blood is to be tested, thereby to provide the presence of said substance in an amount on the same order of magnitude of the concentration of said substance normally found in a test therefor, whereby to reduce the equilibration time required to perform a test for said substance.
  • improved programming and arrangement of valve means enhances the drawing of blood into test stations, and the cyclic cleaning of a plurality of test stations with various fluids.
  • the present invention provides automatic blood withdrawal and/or automatic blood testing with great safety and at a relatively high rate of speed.
  • Blood/- Transparent fluid interface is minimized by a novel reservoir and the interface serves to control the operation of the system.
  • Blood withdrawal apparatus in accordance herewith is capable of withdrawing precise amounts of blood, for use in the automated analysis operations or otherwise, in between the regulated infusion of catheter flushing solution or intravenous irrigation solution.
  • the invention permits rapid cyclic testing of different blood specimens, with automatic washout between tests, and automatic and efficient calibration.
  • the invention eliminates the need for multiple catheters or reconfigurations of withdrawal systems in order to achieve steady state monitoring and infusion in conjunction with periodic blood withdrawal.
  • Blood withdrawal may be achieved utilizing solutions which are compatible with blood testing, or utilizing intravenous irrigation solutions which avoid a buildup of excessive concentrations of undesirable compounds in the blood.
  • the automated testing of blood is achieved in accordance with the invention in a manner utilizing extremely small amounts of blood and returning substantially all withdrawn blood to the patient. Minute amounts of blood used for certain tests are exhausted to waste, thereby avoiding any risk of cross contamination and blood damage problems. Testing of blood from a plurality of automatic or manually withdrawn specimens in a relatively short period of time is readily achieved, clue not only to the complete autonomy of the automated withdrawal and testing units, but as well to fast and efficient washout and calibration procedures.
  • One analysis unit can Service several withdrawal units.
  • the withdrawal unit may be constructed to both infuse l.V. fluid and withdrawal blood, with l.V. fluid being exhausted to waste during the withdrawal mode.
  • calibration fluids drive the blood within the system.
  • FIG. 1 is a simplified block diagram of a system in which the present invention may be incorporated;
  • FIG. 2 is a schematic block diagram of an automated blood withdrawal unit in accordance with the present invention.
  • FIG. 3 is a schematic block diagram of an automated blood analysis unit in accordance with the present invention.
  • FIG. 4 is a simplified schematic block diagram of a timing unit which may be used in conjunction with the embodiment of the invention illustrated in FIGS. 2 and
  • FIG. 5 is a diagram illustrating a mode of cyclically timing the apparatus of the embodiments of FIGS. 2 and 3;
  • FIG. 6 is a perspective representation of a preferred fluid reservoir.
  • a blood analysis system 20 which may incorporate the precepts of the present invention includes one or more withdrawal units 22, an analysis unit 24 and a timing unit 26, which may be included within a calculation unit 28 (not shown) if desired, or may be provided separately as shown herein. Even though more than one withdrawal unit may be used, on a consecutive basis, to deliver blood to the analysis unit, physical isolation, as explained more thoroughly hereinafter, avoids cross contamination.
  • the calculation unit 28 may include indicators 30 if desired, or these may be provided separately, such as at an intensive care unit nurses station or other remote location. The calculation unit 28 may, if desired.
  • the calculation unit 28 may comprise a computing system, such as a large scale computer which may be time shared with other functions, or a minicomputer dedicated to operation with a withdrawal unit 22 and an analysis unit 24 of the type disclosed herein.
  • the timing functions may be readily provided thereby, rather than by a discrete timing unit 26 of the type described with respect to FIG. 4 hereinafter.
  • the apparatus which provides the timing and calculation of test results is not germane to the present invention; instead, the present invention is concerned with the improvements in the withdrawal unit 22 as described with respect to FIG. 2 hereinafter and in the analysis unit 24 as described with respect to FIG. 3 hereinafter, and with the timing of functions performed thereby so as to achieve new and improved operational functions and results.
  • a fitting-32 which may be of the well known Luer type of fitting, is adpated for connection with a suitable arterial, venous, or umbilical catheter 33 of any type known for use in fluid communication with the blood system of the patient.
  • the fitting 32 is connected by tubing 34 to an oximeter 36 which is provided with electrical inlet connections 38 and electrical output connections 40.
  • the tubing 34 must be essentially impervious to diffusion of gas to prevent or minimize O and CO losses. KEL-F and nylon tubing have proved satisfactory.
  • the oximeter 36 may be of any well known type which typically measures oxygen saturation.
  • the oximeter 36 is calibrated with saline in the tubes of the withdrawal unit which remains there and is used as the medium for displacing blood within the withdrawal unit.
  • the oximeter 36 is connected by tubing 42 to a fitting 44 and by means of additional tube 46 to a pair of air detectors (AD) 48, 50.
  • the air detectors 48, 50 include and electric signal input 52 and respective signal outputs 54, 56. It is to be noted that the air detector output terminals 54, 56 are depicted in a circular configuration in contrast with the square configuration of the oximeter output terminals 40. This is to distinguish between electrical signals which are used directly in the control of the system of the present invention (such as signals at the terminals 54, 56) which are depicted in round configuration, from output signals which are used externally of the system so as to derive information relating to blood which is being tested (such as signals at the terminals which are depicted in the square configuration.
  • the air detector is connected by tubing 58 to a port 60 of a fluid valve 62 which,
  • valves herein is depicted schematically as a block having a pair of solid lines illustrating fluid paths 64, 66 which are normally connected or conductive to fluid when the valve is in its normal or deenergized, state, along with dashed lines depicting flow paths 70, 72 which are normally not connected and not conductive to fluid when the valve is in its normal, deactivated, or deenergized state.
  • the port 60 is connected by the path 64 to a port 74 and a port 76 is connected by path 66 to a port 78 when the valve is deenergized as shown in FIG. 2.
  • ports 60, 78 are interconnected by the path and ports 74, 76 are connected by the path 72 when the valve is activated or energized in response to an electric signal applied at a terminal 80a.
  • the valve 62 along with other similar valves herein, is designed to be resiliently urged into the inactivated state by a suitable means such as a spring so that all flow will stop in the event of a power failure, or in the event of detecting air in the blood by the air detectors 48, 50 (in a manner to be described hereinafter).
  • the valve 62 (and other similar valves) may be a pneumatically actuated valve, the pneumatic actuation in turn being in response to an electrically operated solenoid valve. Valves of this type are made by several manufacturers and are available in the marketplace.
  • the port 74 is connected by tubing 82 to an I.V. source and pump apparatus 84 which may be of any conventionel type used for irrigation and/or infusion purposes.
  • the I.V. source and pump 84 With the valve 62 deenergized as shown in FIG. 2, the I.V. source and pump 84 is connected through the valve 62, the air detector 50, the connector 44 and the oximeter 36 to the collector 32 for fluid communication with a catheter.
  • valve 62 When valve 62 is energized, blood is withdrawn from the patient and I.V. solution from 84 is exhausted to waste through port 76 and conduit 112. In this way no damage to the system results which would otherwise threaten because of pressure forces.
  • the I.V. source and pump 84 may be used to infuse intravenous solution into the patient through the catheter at 32.
  • the air detector 48 is connected by tubing 86 to a port 88 of a valve 90, another port 92 of which is connected by tubing 94 to the port 78.
  • a port 96 is connected by tubing 98 to a pressure transducer 100, a single path valve 102, and a flow restrictor 104.
  • the valve 102 may be actuated at 103 to conduct fluid by manual application, so as to use the saline source 110 with a high flow rate for flushing out various lines.
  • the pressure transducer can be of any type well known for the purpose of deriving the patients blood pressure, and provides an electricalsignal indicative thereof at an output terminal 106.
  • This signal may be utilized in any well known fashion, and the transducer forms no part of the present invention.
  • the valve 102 and flow constrictor 104 are connected by tubing 108 to an 8 psi saline solution source 110. With the valve 102 closed as shown, the flow constrictor 104 will provide a very minute, constant, low-pressure flow of saline to the tubing 98 which may be used as a constant flush system to prevent clotting at the end of the catheter connected to the connector 32 during prolonged use, between withdrawal cycles. It should be noted that this function of the apparatus is unnecessary when irrigation is being regularly provided from the I.V. source 84, as described hereinbefore.
  • the saline from the source 110 is normally passed by valves 90, 62 through the port 76 and a suitable means 112 to waste.
  • the means 112 may comprise tubing leading to a waste bucket, or it may simply comprise a syringe attached directly to the port
  • the valve 90 includes a port l14'connected by tubing 116 to a port 118 of a valve 120, which includes a port 122 connecting with a means 124 leading to a blood cup which is described hereinafter with respect to P16. 3.
  • the means 124 may otherwise comprise tubing leading to any receptacle for blood, or a syringe to receive blood which may be attached directly to the port 122.
  • the valve also includes a port 126 leading to tubing 128 which is provided in sufficient length (such as by inclusion of loops 130 therein) to serve as a reservoir on the order of two milliliters in capacity.
  • the other end of the tubing 128 is connected to a port 132 of a valve 134 which includes a port 136 connected by tubing 138 to a constant volume pump 140.
  • the exact nature of the constant volume pump is immaterial to the present invention with the exception of the fact that if the pump 140 provides a constant known volume of fluid per unit of time that it is actually actuated, the volume displacement for a complete stroke also will be constant.
  • the pump 140 may comprise a syringe driven by a piston within a cylinder, the piston in turn being driven by air supplied thereto over tubes 142, 144 under control of a valve 146 which is connected by a tube 148 to a source 150 of air at psi (for instance).
  • the valve in turn is responsive to an OR circuit 152 so that it will be actuated in response to signals applied on a terminal 154 or on a terminal 156.
  • valve 146 With the valve 146 deactivated as shown, air is applied over the tube 144 to cause a cycle which pushes blood from the source 140; when the OR circuit 152 is energized by a signal on either of the terminals 154, 156, it activates the valve 146 to apply air pressure from the source 150 to the tube 142 and cause a cycle which draws fluid into the pump 140.
  • the valve 120 may be activated by a signal from an OR circuit 158 in response to electric signals at either of two terminals 160, 80c.
  • Provision of the OR circuits 152, 158 permits operation of the pump 140 and the valve 120 in response to diverse controls; similarly, the valve 134 is actuated in response to an electric signal from an OR circuit 162 which in turn may operate in response to electrical signals applied on either of two terminals 164, 80d, in a manner which is described in detail hereinafter with respect to FIGS. 4 and 5. Briefly, by actuating the valves 62, 90, 120 and 134 by the simultaneous application of electric signals to terminals 80a, 80b, 80c, and 80d, the
  • air detector 50 (and therefore a catheter connected tothe connector 32) will be connected to the pump 140, and the LV source 84 will be vented through the path 72 to waste.
  • This enables making a short stroke with the pump 140 so as to draw blood into the oximeter 36 for the purpose of monitoring blood oxygen saturation, which can be done frequently with substantially no blood loss or interruption of any other functions; such a test is extremely useful, when performed on a frequent, cyclic basis, to provide an indication of when a more complete blood analysis may be required.
  • the valve 134 includes a port 132 connected by tubing 128 to a saline reservoir 130; this is used, as is described more fully hereinafter with respect to FIGS. 4 and 5, to aid in the withdrawal of blood from (and return of a portion of the blood to) the patient, the insertion of some of the blood in the blood cup for analysis. and in washing out the system.
  • the reservoir 130 takes the form shown in FIG. 6, i.e., a constant diameter small bore tubing 128 coiled as at 130 about a suitable retainer such as the cylindrical retainer 171.
  • the tubing 128 presents a female port 173, through which additional saline may be introduced to replenish the supply. This configuration has been found to solve the heretofore substantial problem of blood/fluid interface mixing. By restricting the blood/saline interface, infused saline is minimized.
  • the valve 134 also has a port 172 which is shown connected to a connector 174 having a plug 176 therein.
  • the port 172 may advantageously be used with a manual flush syringe, if desired.
  • the valve 120 is provided with an additional port 178 which is connected to connector 180 blocked off by a plug 182.
  • the connector 180 may be used to facilitate connection to the valve 120 of pressure transducer apparatus and saline flush apparatus similar to the apparatus 98-110 described hereinbefore. With such an arrangement, constant flush may be provided through the valves 90, 120, when deenergized as shown, and through the air detector 48 to the catheter connected to the connector 32. Then, if desired, a second catheter may be connected to the connector 44 (disconnecting the tube 46 from the tubing 42) so as to allow the running of two systems simultaneously, the catheter connected to the connector 44 being operable either in conjunction with a constant saline flush or in conjunction with an IV. irrigation. as described hereinbefore. in dependence upon the setting of the valve 62. This illustrates the versatility of the present invention.
  • an embodiment of an analysis unit 24 in accordance with the present invention includes a blood cup which may receive blood manually from a syringe, or by being properly disposed may receive blood by other means 124 (FIG. 2) from one withdrawal unit.
  • the blood cup 190 represents a distinct interface between the withdrawal unit and the analysis unit permitting blood to reach the analyzer by force of gravity but preventing analyzer fluids from reaching the patient by maintaining a distinct physical separation between the units.
  • the analyzer fluids (calibration gases and liquids) and the components of the analyzer need not be sterile. As a result all constraints required by a sterile analyzer are removed and the analyzer may be used on one patient after another without appreciable time delay.
  • the blood cup 190 may receive a water washout solution over tubing 192, and either of two buffer solutions over tubing 192, 194.
  • the tubing 192-194 is connected to respective check valves 196198 which are in turn connected by respective tubing 200-202 to additional check valves 204206 and to corresponding syringe pumps 208210.
  • the pumps 208-210 provide a push stroke in response to electric signals applied to corresponding terminals 212214.
  • the volumetric capacity of the pumps is such that upon release of the signals on terminals 212-2l4 the pumps provide draw cycles through the check valves 204-206 to supply the desired amount of fluid to be driven through the check valves 196-198 upon the next energization of the pumps by the application of electric signals at the terminals 212-214.
  • the check valves 204-206 are connected to a source 216 of water and to sources 218, 220 of two different buffer solutions.
  • the buffer one solution in the source 218 may comprise a dilute solution of Na HPO and KH and P0 having a pH of about 7.45, and the buffer two solution in the source 220 may be a dilute solution of Na HPO, and KH P0 having a pH of about 6.88.
  • the two different pHs allow for two calibration points on a pH test as described hereinafter.
  • the blood cup 190 is connected by tubing 222 to a port 224 of a valve 226 which alternatively connects the blood cup 190 to tubing 228 of a pH tester 230 and through tubing 232 connected to a blood gas tester 234.
  • An important feature of the present invention is the utilization of the pH tester 230 to check the blood gas tester 234 for leaks.
  • a means 236 is provided to insure that the liquid in the tubing 228 and in the tubing 232 are at the same electrical potential.
  • the means 236 illustrated in FIG. 3 may comprise a stainless steel wire which passes through the walls of the respective tubing 228, 232 so as to provide for an electrical conduction therebetween.
  • the tube 228 provides fluid connection to a pH electrode 238 which may be of any conventional known type that provides an electric signal at an output 240 which, in conjunction with a reference electrode signal at an output terminal 242 provides a measure of the pH of the fluid therein.
  • the electric output terminal 242 is connected to a reference electrode 244 of the type known in the art, which may be connected by tubing 246, or in any other suitable fashion, to the primary electrode 238.
  • the reference electrode 244 is connected by tubing 248 to a blood detector 250 which may be of any conventional type, such as a photodetector system which senses the opacity of the fluid therein, thereby recognizing the difference between blood and either gas or saline solution.
  • the blood detector 250 is provided with an electric current applied over an input terminal 252 to operate a light source therein, and the photo-detector therein provides an electric signal at an output terminal 254 which is a measure of the transmissivity of the fluid flowing therein. Since this is of conventional nature and forms no part of the present invention, further description is not given herein.
  • the sensing of the blood/fluid interface at blood detector 250 and/or blood detector 268 controls the positioning of blood which is pulled from the cup and accordingly, the needed volume of blood. If blood is not sensed within a predetermined time, an error is indicated, measurement is terminated and the system is flushed. In thisway the amount of blood used by the analyzer and not returned to the patient is minimal.
  • the blood detector is connected by tubing 256 to a port 258 of a valve 260 which is always operated in conjunction with the valve 226 by simultaneous application of electric operating signals to a pair of input terminals 262a, 262b, as is described more fully hereinafter.
  • the tubing 232 is connected to gas electrodes 264 which provide electric singals at a pair of output terminals 267, 268.
  • the gas electrodes may be conventional membrane-type electrodes for measuring P0 and PCO and form no part of the present invention.
  • the gas electrodes 264 are connected by tubing 266 to a blood detector 268 which is similar to the blood detector 250 including an electric input terminal 270 and an electric output terminal 272.
  • the blood detector 268' is connected by tubing 274 to another port 276 of the valve 260.
  • the valve 226 When deenergized, the valve 226 provides flow of blood from the blood cup 190 into the blood gas detector 264 and through the port 278 to port 279 of a pump valve 280.
  • valve 226 When energized, the valve 226 connects the blood cup 190 to the pH tester 230 and connects the gas detector 234 through a port 282 to tubing 284 or other suitable waste disposition means.
  • valve 260 When the valve 226 is energized, the valve 260 is also energized, connecting the pH tester 230 through the port 258 of valve 260 to port 279 of the pump valve 280, but also connecting the gas tester 234 through ports 276 and 286 of valve 260 to a port 288 of a calibration gas valve 290 by a tubing 291.
  • the pump valve 280 includes a port 292 connected to a constant volume pump 294 and a port 296 connected by a suitable tubing 298 or other means to a proper disposition for liquid waste.
  • the port 288 of the valve 290 is normally connected through a port 302 and tubing 304 to a flow constrictor 306 which in turn is connected by tubing 308, a valve 309 (operated by a signal at a terminal 310). and tubing 311 to a source 312 of a high P0 and PCO
  • the tubing 308 also applies such to a variable flow constrictor 313 which is provided with a manual adjustment 314 to adjust the amount of flow therethrough.
  • This provides gases from the source 310 to the water source 216 over tubing 316, thereby to provide sufficient carbonate in the water of the source 216 so that the gas electrodes 264 will, after being washed with water from the source 216, have a substantial carbon dioxide concentration diffused through the membranes prior to a final calibration gas to drive washout water through the unit, the concentrations will not be so depleted in the gas electrodes 264 so as to require an undue equilibration time for a final test after all blood is washed therefrom.
  • the valve 290 when activated by an electric signal at an input terminal 320, connects its port 288 with a port 322 and tubing 324 to another flow restrictor 326 which is connected by tubing 328 to a source 330 of low P0 and PCO Since the sources 312, 330 are under pressure, they are used, as described hereinafter, in the process of cleaning out the gas electrodes 264.
  • the analyzer is calibrated before blood is introduced. Specifically, a liquid calibration fluid is used to calibrate pH electrode 238 and a gas calibration fluid is used to calibrate gas electrodes 264. Thereafter, the calibration fluids are retained in the analyzer and used. responsive to negative pressure, to displace blood within the analyzer after it is received at cup 190. In this way the calibration is preserved.
  • the timing unit 26 includes some source of ordinary power 340 which is assumed to include means 342 for turning it on and off. Such power may simply comprise cycle 120 volt power.
  • the source 340 is connected by a line 344 to a onesixth revolution per minute motor 346 through a normally open switch 348 and a line 350.
  • the switch 348 is normally open and must be activated by a signal on a line 352 from an OR circuit 354 in order to apply power from the line 344 to the motor 346.
  • the motor is connected by shafts 356, 357 to a one track rotary timer 358 and a sixteen track rotary timer 359.
  • the timers 358, 359 are supplied power from a valve power source 360 over a line 361.
  • an oximeter ON switch 364 may be closed applying power from the line 361 to a set input of a latch 365 which provides a signal on a line 366 to operate the OR circuit 354 and apply power to the motor 346.
  • the signal on the line 366 applies power to the terminal which in turn is applied in FIG. 2 to all of the terminals 80a80d.
  • a single contact element per revolution is provided, so as to provide a signal on a line 368 to the terminal 154 which will cause the OR circuit 152 (FIG. 2) to operate the valve 146 and initiate a short stroke of the pump 140.
  • the length of the signal on the line 368 (and therefore the length of time duration of the pump stroke) may be approximately eight seconds so as to draw approximately 0.5 of a milliliter of blood through the oximeter 36, and then restore it back to the patient.
  • This is readily achieved by providing a contact in the timer 358 which extends over 8 (the same number of degrees as is desired seconds since the one-sixth rpm motor 346 will cause the timer to complete one revolution in 360 seconds 6 minutes).
  • the OR circuit 354 may be operated by a signal on a line 374 in response to the setting of a bistable device such as a trigger or latch 376 whenever full automatic withdrawal and analysis cycles are being performed under the control of the l6-track rotary timer 359.
  • the 16-track timer 359 has l6-tracks of contacts which are arranged as shown in FIG. 5. If the timer 359 is a drum timer, then FIG. depicts the contact arrangement simply by joining the left end thereof (zero seconds in time and zero arcuate degrees) with the right end thereof (360 seconds in time and 360 arcuate degrees). On the other hand, if the sixteen track timer 359 is arranged in the form of a disc.
  • the OR circuit 382 will also be operated by an OR circuit 384 in response to signals at either of a pair of terminals 54, 56 (FIG. 2) indicating that air bubbles have been detected in the blood lines.
  • the OR circuit 384 may also operate an alarm 396 so as to advise an attendant at an intensive care nurses station or otherwise that air has been detected in the lines.
  • the rotary timer 359 While the rotary timer 359 is operating, it presents signals on a plurality of lines to operate valves and pumps so as to cause direct cyclic operation of both the withdrawal unit and the analysis unit for a complete automatic withdrawal and sampling of blood, together with washout and calibration thereof.
  • Each of the lines at the output of the rotary timer depicted as being within a trunk of fifteen lines 398, is provided with an appropriate legend, and is connected to the electric terminal which it operates in FIGS. 1, 2 or 3.
  • the signal lines 398 from the sixteen track timer 359 include a signal causing a test of the air detectors on a line 399, which operates a normallyopen switch 400 to shortcircuit a resistor 402, so as to provide more current from an LED power source 404 through the terminal 52 to the air detectors 48, 50
  • FIG. 2 This over-powers the air-detectors and forces an alarm condition even though there is liquid in them. unless they are inoperative.
  • a withdrawal pump signal which causes the withdrawal pump 140 (FIG. 2) to initiate a pull stroke. thereby drawing blood into the system from a catheter, is provided to the terminal 156.
  • a withdrawal pump valve signal at terminal 164 operates the valve 134 (FIG. 2) in such a fashion as to connect the pump to the 2 milliliter reservoir 130.
  • a blood cup valve signal applied to a terminal 160 causes the valve (FIG.
  • a sample pI-I signal is applied to a terminal 410 to indicate to any apparatus, such as the calculation unit 28 of FIG. 1, that now is the proper time to sample the output of the pH tester 230 (FIG. 3) at the terminals 240, 242.
  • a sample gas signal is applied to a terminal 412 to indicate to the calculation unit 28, or such other unit as may be used to analyze the results of blood tests, that now is the proper time to sample the output of the gas tester 234 at the terminals 267, 268.
  • a buffer one pump signal applied to a terminal 213 causes the buffer one syringe pump 213 to stroke in the push direction.
  • a high concentration calibration gas signal applied to a terminal 310 causes closure of the valve 309 (FIG. 3) to allow the high concentration calibration gas source 312 to enter the system.
  • the calibration gas valve signal applied to a terminal 320 causes the valve 290 (FIG. 3) to transfer from the normal high concentration connection, as shown. to connect the low concentration source 330 with the port 288.
  • An H O pump signal connected to a terminal 212 causes the syringe pump 208 (FIG. 3) to initiate a push stroke.
  • a buffer two pump signal applied to a terminal 214 causes the syringe pump 210 (FIG. 3) to initiate a push stroke.
  • a gas blood detector signal applied to a terminal 270 powers a light source in the blood detector 268' (FIG. 3) so as to be able to detect the presence of blood.
  • a pH blood detector signal applied to a terminal 252 energizes the blood detector 250 (FIG. 3) so as to be able to detect blood passing therethrough.
  • An analysis pump signal is applied to a terminal 414 for application to the valve 280 (FIG. 3) and to a related valve 416 which is connected in an obvious fashion by tubings 418, 420 to the pump 294.
  • the valve 280 will connect the valve 260 to the pump 294, and the valve 416 will cause the pump 294 to initiate a pull stroke pulling fluid through the valve 292 into the pump 294; at this time, operating air within the pump is exhausted through the tube 418 and the valve 416 through a port 422 to exhaust.
  • the valve 280 Upon removal of the signal on the terminal 414, the valve 280 connects the port 292 with the port 296 and the valve 416 drives air through the tub-
  • the signal on the terminal 414 is generated specially in FIG.
  • OR-invert circuit 430 will operate the AND circuit 426 to provide a signal at the terminal 414 for the operation of the pull stroke of the analysis pump 294 (FIG. 3).
  • a signal on either of the terminals 254, 272 will cause the OR-invert circuit 430 to remove the input to the OR circuit 427, thus terminating the stroke of the pump 294 (FIG. 3).
  • Use of the OR invert circuit 428 precludes the possibility of noise or other spurious signals from blocking the AND circuit 426 when the blood detectors are not turned on. This feature allows drawing just a requisite amount of blood into the pH tester 230 and the gas tester 234 so the blood isnt drawn through other parts of the system thereby necessitating a greater amount of blood and washout.
  • Operation of the device begins with the main power source turned on by the depression of the start switch 380 (FIG. 4) which will cause the latch 376 to become set, overriding a tendency of the OR circuit 382 to reset it, thereby closing the normally open switch 348 so as to apply main power to the one-sixth rpm motor 346.
  • the switch should be depressed for at least a second until the motor can turn sufficiently so as to clear the motor control segment and thus remove the signal on the line 381 so that the motor will continue to run.
  • signals are applied to the terminals 213, 310, 414 and 262 so as to energize the buffer one pump, close the high concentration gas valve, start the analysis unit pump 294 and place the gas/pH valve to the pH side.
  • This causes buffer one to be pushed into the blood cup 190 and drawn by the constant volume pump into the pH tester 230 all the way into the pump 292, while high concentration calibration gas flows into the gas tester 234. All of these signals remain present for seconds.
  • the air detectors in the withdrawal unit are tested. Thereafter, at the twenty-first second, signals are applied to terminals 156, 164 and 160, and the pump in the withdrawal unit (FIG. 2) is actuated at the same time that the pump valve and cup valve are actuated so as to draw blood from the catheter through the connector 32 through the oximeter and the air detector into the port 88 of valve 90 through the valve 120 and into the 2 milliliter reservoir 130. These conditions are maintained for 40 seconds, until about the sixty-first second, although the pump valve 134 is left in the actuated position to connect the 2 milliliter reservoir to the pump all the way to the one hundred first second. While the blood is being drawn into the withdrawal unit.
  • buffer one is flushed out of the pH tester 230 by energizing the water pump (terminal 212), reactivating the gas/pH valve so as to feed pH (terminal 262), and reactivating the pump (terminal 414) for a full cycle so that as water or saline falls into the blood cup, it is drawn all the way down into the pump.
  • These signals are maintained energized for about 20 seconds until about the sixtyfirst second.
  • the signal on terminal 156 and that on terminal 160 are removed so that the withdrawal pump will initiate a-push stroke with the valve deenergized so that blood is pushed from the 2 milliliter reservoir into the blood cup.
  • everything in the analysis unit is deenergized and remains so for approximately 10 seconds to allow theblood to settle down in the blood cup.
  • the valve 120 is actuated after about 7 seconds (which permits pumping substantially 0.4 milliliters into the blood cup) and then it is energized so that the remainder of the blood will be returned to the patient along with approximately 1.5 milliliters of saline. It is to be noted that, prior to starting the operation, saline existed in the lines as a result of initially loading them or as a result of finishing the prior cycle as is described hereinafter.
  • the blood detector 250 After allowing ten seconds for the blood to settle in the cup, at about the seventy-first second, the blood detector 250 is turned on by a signal on terminal 252, and blood is drawn into the pH tester by applying signals to the terminals 262 and 414 so that the gas/pH valve is in the pH position and the pump will initiate a pull cycle. However, as soon as blood reaches the blood detector 250, it will cause (by means of the apparatus at the bottom of FIG. 4 described hereinbefore) deener gization of the signal at the terminal 414 so that the pump stroke stops immediately.
  • the blood in the pH tester 230 is still equilibrating, as is the high concentration calibration gas which entered the gas tester 234 at time zero.
  • the pump in the withdrawal unit (FIG. 2) is caused to make a pull stroke with the valve 134 disenergized to pull saline solution from the source 170 down into the pump.
  • the pH and gas detectors are both sampled at the output terminals 240, 242 and 267, 268. This comprises a first test of the pH of the blood itself and a first calibration test of the gas electrodes 264.
  • the gas blood detector 268' is turned on with a signal at the terminal 270 and the pump is started by applying a signal on the line 414.
  • both the gas and pH are sampled at their terminal 240, 242 and 267, 268 which comprise the first sampling of gas in the blood itself and the second sampling of pH in the blood.
  • the second sampling of pH is to provide an indication of the integrity of the gas electrodes 264; if there is any leakage in the gas electrode 264, such a leak would cause a change in the electrical potential of the blood in the tubing 232, the because of the stainless steel electrical connector 236 between that tubing and the tubing 228, it would also result in a change in the electrical potential of the blood within the pH electrode 238. This would result in a different pH reading than that which was previously obtained.
  • Utilization of a second pH reading of the blood is achieved by calculations performed in the calculation unit 28 (HO. 1) or in a computer if one is used, or simply a substantial difference in pH reading indicates to the operator that there is likely to be a fault in the gas electrodes 264. This is an important feature of the present invention.
  • flushing of the blood from the pH tester 230 and the gas tester 324 commences. This is achieved by closing the high gas relay 309, energizing the high/low gas valve 290 so that the low concentration calibration gas is available, energizing the gas/pH valves 226 and 260 so as to permit flow into the pH side and starting the pump by applying a signal to the terminals 414.
  • the high gas valve 309 is closed to permit leakage of gas from the source 312 into the water source 216 so as to increase the carbon content thereof.
  • saline is drawn from the blood cup down into the pH tester 230.
  • the pump is again shut off for 2 seconds and it pushes the blood and saline which it has drawn from the pH tester 230 outwardly through the port 296 of the valve 280 to waste.
  • the H 0 pump is again energized (212) to cause water to be pushed into the blood cup.
  • the analysis pump is again started at about the two hundredth second and again draws saline and water through the pH detector for three seconds, then the valves 226 and 260 are turned off for 2 seconds so that the pump, instead, draws saline and water into the gas detector 234.
  • valves 226 and 260 are again energized so that saline is drawn into the pH detector, and while this is occurring.
  • the low concentration calibration gas in the source 330 pushes some of the saline out of the gas detector 234 upwardly through the port 282 to liquid waste. This process continues until about the two hundred and twentieth second when the pump is turned off so that it provides a push stroke to push all the waste it has collected from both the pH tester 230 and the gas tester 234 outwardly through the port 296 to waste.
  • the pump again discharges waste that it has collected from both the pH tester 230 and the gas tester 234, during which time the valves 226 and 260 have cycled, and while in the energized position the low concentration calibration gas of the source 330 has pushed waste upwardly out of the gas tester 234.
  • the pump and the pH/gas valve are again turned on at the same time as the buffer number two pump is turned on so that buffer number two begins to be pumped into the blood cup 190 and this is drawn into the pH tester 230. This is completed 20 seconds later, at about the two hundred and sixty-fourth second.
  • the low concentration calibration gas of the source 312 has been continuously running into the gas tester 234 and venting outwardly through the port 282 to waste.
  • the pH tester 230 is filled with buffer number two and thegas tester 234 is filled with low concentration calibration gas from the source 330.
  • An equilibration period of 45 seconds then passes following which, at the three hundred and ninth-second, both pH and gas are again sampled at their terminals 240, 242 and 267, 268 for a final calibration of both the pH and gas testers 230, 234.
  • the calibration provides corrections for changes in sensitivity and drift of the electrodes.
  • the loading of water and purging of gas in the gas electrode 264 is accomplished, beginning at the three hundred and tenth second, by energizing the water pump by means of a signal at the terminal 212 so as to commence to pump water into the blood cup 190 at the same time that the pump is operated by providing a signal at the terminal 414 while leaving the valves 226 and 260 deenergized so that the clean water is drawn into the gas tester 234.
  • the pump is deactivated for two seconds to allow dumping the mixture of gas and water out to liquid waste, following which it is again activated to pump the remaining water out of the blood cup 190 into the gas tester 234.
  • the motor will therefore stop when the sixteen track rotary timer is set on the contact that provides the motor control signal on line 381.
  • the embodiment of the invention described hereinbefore thus provides a very compatible blood withdrawal unit which, according to the invention, may withdraw blood through lines filled with saline so as to preserve the integrity of tests to be performed on blood, or may withdraw blood through lines filled with l.V. irrigation solutions, thereby to minimize the opportunity for sodium buildup in the patient.
  • the described embodiment provides for final calibration of gas and pH testers after testing of blood, in addition to initial calibrations before the testing of blood.
  • Carbonation of washout water in the gas tester provides for the preestablishment of a certain level of carbonate in the gas detector to reduce the time necessary for equilibration thereof, and in further accord with the invention, valving between the pH tester and the gas tester permits simultaneous washout utilizing a single pump, in combination with the use of calibration gas to completely flush, forwardly and backwardly, the gas electrode, while simultaneously performing a forward flush of the pH electrode.
  • An automated blood unit comprising: first and second fluid valves, each having a normal position and an operated position;
  • a first fluid path means adapted to be connected to an indwelling blood catheter for interconnecting said catheter with a first port of said first fluid valve
  • a second fluid path means connected to said first fluid path means and to a first port of said second fluid valve
  • a third fluid path means interconnecting a second port of said second fluid valve with a second port of said first fluid valve
  • said first fluid valve comprising first fluid communicating means, when in its normal position. connecting said first fluid path means with said pump, and also comprising second fluid communicating means when in its operated position. connecting said third fluid path means with said pump via the interconnecting means, and said second fluid valve comprising first fluid communicating means, when in its operated position, connecting said second fluid path means with said third fluid path means, so that, with a catheter connected (a), in response to said pump initiating a draw cycle with said first fluid valve in its normal position, fluid is drawn by force of said pump along a pathway comprising said first fluid path means, said first fluid communicating means of the first fluid valve and said interconnecting means thereby drawing blood from said catheter into said first fluid path means.
  • the automated blood unit according to claim 1 additionally comprising:
  • an intravenous irrigation solution source connected to a third port of said second valve, said third port being connected by second fluid communicating means to said second fluid path means when said second valve is in its normal position, a fourth port of said second fluid valve and third fluid communicating means connecting said fourth port to said third fluid path means at the second portof the second valve when said second valve is in its normal position, said fourth port adapted to discharge to waste fluid passing from the third fluid path means and said third communicating means, said first fluid path being adapted to be filled with saline solution, so that blood is withdrawn from said catheter into said first fluid path means due to negative saline pressure caused by the pump and thereafter returned to said catheter from said first fluid path means in response to positive fluid pressure created by the pump against the saline and thence against the blood when said fluid valves are in their normal positions, and blood is withdrawn from said catheter through the first fluid path means into said secnd fluid path means due to negative saline pressure caused by the pump and thereafter returned to said catheter from said second fluid path means along said first fluid path means in response to positive fluid
  • said first fluid path means includes an oximeter disposed between the junction of said second fluid path means with said first fluid path means and the point of connection of said catheter to said first fluid path means and wherein the oximeter comprises means for taking oximeter readings by pump drawing a small sample of blood along the first fluid path means through the oximeter and then pump displacing at least a portion of the blood sample back along the first fluid path means into the patient.
  • connection means for connecting said second fluid path means with said first fluid path means, said connection means being adapted for connection to a second indwelling catheter in lieu of the first fluid path means.
  • the automated blood unit according to claim 1 additionally comprising:
  • a low pressure constant flow saline source connected by fourth fluid path means to a fourth port of said first valve
  • said first valve comprising a third fluid communicating means which, when the first valve is in its normal position, connects said saline source with said third fluid path means
  • said first fluid valve also comprising fourth fluid communicating means which, when said first valve is in its operated position, connects said saline source with said first fluid path means
  • the second fluid valve comprising an additional port being connected by additional fluid communicating means to said third fluid path means, when said second valve is in its normal position, said fourth port adapted to discharge fluid passing therethrough to waste, so that said first fluid valve (a) connects said first fluid path means with said pump via said first fluid communicating means of the first valve and the interconnecting means and connects said saline source with waste via said third fluid communicating means of the first fluid valve, the third fluid path means, the additional fluid communicating means and the additional port of the second fluid valve, when said first and second valves are in their normal positions, and (b) connects said s
  • the automated blood unit according to claim 5 including a blood pressure transducer in fluid communication with one of said pathways.
  • a blood testing system comprising:
  • a catheter to be introduced through the skin into the cardiovascular system ofa patient using a sharp instrument; a blood withdrawal unit connected to the catheter.
  • the blood withdrawal unit comprising a closed fluid storage system comprising fluid pathway means comprising flexible tubing, the pathway having a uniform small bore throughout.
  • which pathway means are initially filled with biologically inert fluid
  • blood flow means including two directional power means imposing positive and negative pressures upon the inert fluid within the pathway means for withdrawing blood, under negative pressure, through the catheter into and expelling all of the withdrawn blood from the withdrawal unit under positive pressure
  • said blood flow means comprising means for causing at least a substantial portion of the withdrawn blood to be returned through the pathway means and the catheter into the cardiovascular system under negative pressure caused by said power means, whereby upon withdrawal of blood through the catheter into the uniform bore pathway means of the withdrawal unit said blood flow means causes little if any turbulent flow resulting in an essentially two dimensional blood/fluid interface comprising a negligible amount of fluid with little or no mixing of blood and fluid and, thereafter, causing return of substantially all blood along the pathway means and into the cardiovascular system through the catheter and infusion into the cardiovascular system of very little inert fluid under
  • An automated blood testing system comprising:
  • a catheter to be placed in the cardiovascular system of a patient through venipuncture
  • a blood withdrawal unit comprising fluid passageway means in fluid communication with the catheter, biologically inert fluid in said passageway means, at
  • test station disposed at a site intermediate the passageway means, and two way hydraulic pressure control means for removing blood juxtaposed the inert fluid through the catheter and along a path comprising said passageway means to said test station under hydraulic pressure at the same time withdrawing said inert fluid along the same path thereby creating a movable interface between the blood and fluid;
  • said withdrawal unit further comprising means at said test station site for testing said blood disposed in said passageway means at said station and means creating hydraulic pressure which acts upon said inert fluid to jointly displace the inert fluid and blood in a reverse direction along said path and thereby return essentially all of said removed blood to the patients cardiovascular system through the catheter, said two way control means having means terminating the return of blood to the cardiovascular system when the blood/fluid interface is juxtaposed the catheter.
  • An automated blood testing system comprising:
  • each withdrawal unit adapted to be coupled to a patient via a catheter placed through the skin into a vessel by a sharp instrument and each withdrawal unit defining an independent blood flow path therethrough;
  • a single non-sterile blood analysis unit comprising one-way blood ingress means which receives blood from any selected one of said withdrawal units at any specified point in time, passageway means connected to the one-way blood ingress means, a plurality of blood testing sites disposed at various locations along the passageway means, each blood testing site comprising means for evaluating blood, means for displacing blood received at the one-way blood ingress means along the passageway means to each testing site, and blood egress means for expelling blood from the analysis unit to waste;
  • each withdrawal unit comprising means for removing blood from a patient through the associated catheter and flow path of the associated withdrawal unit to the one-way blood ingress means of the analysis unit and for returning blood to the patient which, following withdrawal, is disposed within the flow path of said withdrawal unit between the catheter and the one-way blood ingress means of the analysis unit.
  • An automated blood testing system comprising:
  • a sterile blood withdrawal unit adapted to be coupledv to a patient via a catheter placed through the skin into a vessel by a sharp instrument, the withdrawal unit defining a blood flow path therethrough;
  • a non-sterile blood analyzer comprising a one-way blood ingress interface in oneway communication with the blood flow path to receive blood from the withdrawal unit, the one-way blood ingress interface comprising means preventing blood flow from the analyzer back to the withdrawal unit, and passageway means connected to the one-way blood ingress interface, at least one blood testing site disposed at a location along the passageway means, the blood testing site comprising means for evaluating blood, means for displacing blood received from the withdrawal unit at the one-way blood ingress interface along the passageway means to the testing site, blood egress means for expelling blood from the analyzer to waste;
  • the withdrawal unit comprising means for removing blood from the patient through the catheter and flow path of the withdrawal unit to the one-way blood ingress interface of the analyzer and for returning to the patient residual blood disposed within the flow path of the withdrawal unit between the catheter and the one-way blood ingress interface.
  • the blood flow preventing means of the one-way blood ingress interface comprise a blood effluent tube comprising part of the withdrawal unit and a blood collection chamber comprising part of the analyzer, the blood collecting chamber being physically separated from the cffluent tube and into which blood from the effluent tube is discharged.
  • a catheter to be introduced into a patient by a needle
  • a blood withdrawal/intravenous infusion apparatus having means operating in a withdrawal mode and means operating in an infusion mode comprising:
  • blood withdrawal passageway means in fluid communication with the catheter, at least one blood monitoring site along the passageway means comprising means for evaluating blood, power means for withdrawing blood through the catheter and passageway means to the monitoring site when the withdrawal operating means are caused to function,
  • control means for shifting the unit between said two modes
  • infusion means comprising a source of infusion fluid a first flow path comprising part of said passageway means including the blood monitoring site spanning between the source of infusion fluid and the catheter, a second flow path spanning between the source and a waste station, and pressure-creating means to drive the fluid along (a) the first flow path when the control means have set the infusion operating means to function and (b) the second flow path when the control means have set the withdrawal operating means to function.

Landscapes

  • Analytical Chemistry (AREA)
  • General Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Quality & Reliability (AREA)
  • Biochemistry (AREA)
  • Engineering & Computer Science (AREA)
  • General Physics & Mathematics (AREA)
  • Immunology (AREA)
  • Pathology (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Investigating Or Analysing Biological Materials (AREA)
  • Automatic Analysis And Handling Materials Therefor (AREA)
US00319561A 1972-12-29 1972-12-29 Automated blood analysis system Expired - Lifetime US3838682A (en)

Priority Applications (6)

Application Number Priority Date Filing Date Title
US00319561A US3838682A (en) 1972-12-29 1972-12-29 Automated blood analysis system
FR7347049A FR2212940A5 (de) 1972-12-29 1973-12-28
JP744318A JPS5649575B2 (de) 1972-12-29 1973-12-28
DE2365048A DE2365048A1 (de) 1972-12-29 1973-12-28 Automatisch arbeitendes blutabnahmevorrichtung
GB5974573A GB1463675A (en) 1972-12-29 1973-12-29 Automated blood analysis system
US490603A US3910256A (en) 1972-12-29 1974-07-22 Automated blood analysis system

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US00319561A US3838682A (en) 1972-12-29 1972-12-29 Automated blood analysis system

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US490603A Division US3910256A (en) 1972-12-29 1974-07-22 Automated blood analysis system

Publications (1)

Publication Number Publication Date
US3838682A true US3838682A (en) 1974-10-01

Family

ID=23242772

Family Applications (1)

Application Number Title Priority Date Filing Date
US00319561A Expired - Lifetime US3838682A (en) 1972-12-29 1972-12-29 Automated blood analysis system

Country Status (5)

Country Link
US (1) US3838682A (de)
JP (1) JPS5649575B2 (de)
DE (1) DE2365048A1 (de)
FR (1) FR2212940A5 (de)
GB (1) GB1463675A (de)

Cited By (49)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3910256A (en) * 1972-12-29 1975-10-07 Primary Childrens Hospital Automated blood analysis system
US4119406A (en) * 1976-05-06 1978-10-10 Miles Laboratories, Inc. Calibration apparatus
US4127111A (en) * 1976-10-26 1978-11-28 Drolet Roland A Automatic blood sampling system and method
JPS54135474A (en) * 1978-02-17 1979-10-20 Radiometer As Method of and device for monitoring ph value of blood plasam in living body
US4231366A (en) * 1976-08-12 1980-11-04 Dr. Eduard Fresenius Chemisch-Pharmazeutische Industrie Kg Apparatebau Kg Blood flow monitoring and control apparatus
US4240438A (en) * 1978-10-02 1980-12-23 Wisconsin Alumni Research Foundation Method for monitoring blood glucose levels and elements
US4253456A (en) * 1977-08-23 1981-03-03 Dr. Eduard Fresenius Chemisch-Pharmazeutisch Industrie Kg, Apparatebau Kg Artificial endocrinal gland
US4258717A (en) * 1977-09-06 1981-03-31 Institute Of Critical Care Medicine Vascular interface
US4316466A (en) * 1980-06-27 1982-02-23 Biomedics, Inc. Body fluid drainage device
US4370983A (en) * 1971-01-20 1983-02-01 Lichtenstein Eric Stefan Computer-control medical care system
US4615340A (en) * 1985-02-27 1986-10-07 Becton, Dickinson And Company Sensor assembly suitable for blood gas analysis and the like and the method of use
US4717548A (en) * 1980-06-09 1988-01-05 The United States Of America As Represented By The Secretary Of The Department Of Health And Human Services Analytically controlled blood perfusion system
EP0389719A2 (de) * 1989-03-27 1990-10-03 International Technidyne Corp System zur Aufnahme und Abgabe flüssiger Proben und speziell an die Körperflüssigkeitsprobenahme angepasste Methode
US5533512A (en) * 1994-03-18 1996-07-09 Ohmeda Inc. Method and apparatus for detection of venous air emboli
US5758643A (en) * 1996-07-29 1998-06-02 Via Medical Corporation Method and apparatus for monitoring blood chemistry
US20070179437A1 (en) * 2006-02-02 2007-08-02 Henry Grage Method and apparatus for testing blood glucose in a reversible infusion line
US20080119703A1 (en) * 2006-10-04 2008-05-22 Mark Brister Analyte sensor
US20080306434A1 (en) * 2007-06-08 2008-12-11 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US7640048B2 (en) 2004-07-13 2009-12-29 Dexcom, Inc. Analyte sensor
US7783333B2 (en) 2004-07-13 2010-08-24 Dexcom, Inc. Transcutaneous medical device with variable stiffness
US7885697B2 (en) 2004-07-13 2011-02-08 Dexcom, Inc. Transcutaneous analyte sensor
US8275438B2 (en) 2006-10-04 2012-09-25 Dexcom, Inc. Analyte sensor
US8287453B2 (en) 2003-12-05 2012-10-16 Dexcom, Inc. Analyte sensor
US8298142B2 (en) 2006-10-04 2012-10-30 Dexcom, Inc. Analyte sensor
US8364230B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US8364231B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US8396528B2 (en) 2008-03-25 2013-03-12 Dexcom, Inc. Analyte sensor
US8425417B2 (en) 2003-12-05 2013-04-23 Dexcom, Inc. Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion device
US8425416B2 (en) 2006-10-04 2013-04-23 Dexcom, Inc. Analyte sensor
US8447376B2 (en) 2006-10-04 2013-05-21 Dexcom, Inc. Analyte sensor
US8449464B2 (en) 2006-10-04 2013-05-28 Dexcom, Inc. Analyte sensor
US8478377B2 (en) 2006-10-04 2013-07-02 Dexcom, Inc. Analyte sensor
US8562528B2 (en) 2006-10-04 2013-10-22 Dexcom, Inc. Analyte sensor
US8626257B2 (en) 2003-08-01 2014-01-07 Dexcom, Inc. Analyte sensor
WO2014015691A1 (zh) * 2012-07-20 2014-01-30 深圳市麦迪聪医疗电子有限公司 一种血气分析仪及其使用方法
US8886273B2 (en) 2003-08-01 2014-11-11 Dexcom, Inc. Analyte sensor
US9986942B2 (en) 2004-07-13 2018-06-05 Dexcom, Inc. Analyte sensor
US10610137B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10813577B2 (en) 2005-06-21 2020-10-27 Dexcom, Inc. Analyte sensor
US10835672B2 (en) 2004-02-26 2020-11-17 Dexcom, Inc. Integrated insulin delivery system with continuous glucose sensor
US10966609B2 (en) 2004-02-26 2021-04-06 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US10980461B2 (en) 2008-11-07 2021-04-20 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US11000215B1 (en) 2003-12-05 2021-05-11 Dexcom, Inc. Analyte sensor
US11246990B2 (en) 2004-02-26 2022-02-15 Dexcom, Inc. Integrated delivery device for continuous glucose sensor
US11331022B2 (en) 2017-10-24 2022-05-17 Dexcom, Inc. Pre-connected analyte sensors
US11350862B2 (en) 2017-10-24 2022-06-07 Dexcom, Inc. Pre-connected analyte sensors
US11399745B2 (en) 2006-10-04 2022-08-02 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US11416397B2 (en) * 2019-10-14 2022-08-16 Intel Corporation Global persistent flush
US11633133B2 (en) 2003-12-05 2023-04-25 Dexcom, Inc. Dual electrode system for a continuous analyte sensor

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8879715B2 (en) 2012-03-26 2014-11-04 Satmap International Holdings Limited Call mapping systems and methods using variance algorithm (VA) and/or distribution compensation
US10708430B2 (en) 2008-01-28 2020-07-07 Afiniti Europe Technologies Limited Techniques for benchmarking pairing strategies in a contact center system
US9025757B2 (en) 2012-03-26 2015-05-05 Satmap International Holdings Limited Call mapping systems and methods using bayesian mean regression (BMR)
US8792630B2 (en) 2012-09-24 2014-07-29 Satmap International Holdings Limited Use of abstracted data in pattern matching system
US10326882B2 (en) 2016-12-30 2019-06-18 Afiniti Europe Technologies Limited Techniques for workforce management in a contact center system
US10970658B2 (en) 2017-04-05 2021-04-06 Afiniti, Ltd. Techniques for behavioral pairing in a dispatch center system
US10122860B1 (en) 2017-07-10 2018-11-06 Afiniti Europe Technologies Limited Techniques for estimating expected performance in a task assignment system

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2455810A (en) * 1945-06-08 1948-12-07 Ryan William Device for inspecting blood circulation
US2700320A (en) * 1949-05-28 1955-01-25 Jefferson Medical College Of P Cuvette cell assembly for extracorporeal circulation devices
US3029682A (en) * 1959-07-17 1962-04-17 Research Corp Apparatus for determining percentage oxygen-saturation of blood
US3043303A (en) * 1958-07-11 1962-07-10 Joseph W Still Method and apparatus for utilizing the permanent long term aorta intubation of a laboratory animal
US3489145A (en) * 1966-08-08 1970-01-13 Surgeon General Of The Public Method and apparatus for continuous separation of blood in vivo
US3648694A (en) * 1968-09-25 1972-03-14 Inst Oncologic Bucharest Automatic system with perfusion protection against malfunction

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2455810A (en) * 1945-06-08 1948-12-07 Ryan William Device for inspecting blood circulation
US2700320A (en) * 1949-05-28 1955-01-25 Jefferson Medical College Of P Cuvette cell assembly for extracorporeal circulation devices
US3043303A (en) * 1958-07-11 1962-07-10 Joseph W Still Method and apparatus for utilizing the permanent long term aorta intubation of a laboratory animal
US3029682A (en) * 1959-07-17 1962-04-17 Research Corp Apparatus for determining percentage oxygen-saturation of blood
US3489145A (en) * 1966-08-08 1970-01-13 Surgeon General Of The Public Method and apparatus for continuous separation of blood in vivo
US3648694A (en) * 1968-09-25 1972-03-14 Inst Oncologic Bucharest Automatic system with perfusion protection against malfunction

Cited By (117)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4370983A (en) * 1971-01-20 1983-02-01 Lichtenstein Eric Stefan Computer-control medical care system
US3910256A (en) * 1972-12-29 1975-10-07 Primary Childrens Hospital Automated blood analysis system
US4119406A (en) * 1976-05-06 1978-10-10 Miles Laboratories, Inc. Calibration apparatus
US4231366A (en) * 1976-08-12 1980-11-04 Dr. Eduard Fresenius Chemisch-Pharmazeutische Industrie Kg Apparatebau Kg Blood flow monitoring and control apparatus
US4127111A (en) * 1976-10-26 1978-11-28 Drolet Roland A Automatic blood sampling system and method
US4253456A (en) * 1977-08-23 1981-03-03 Dr. Eduard Fresenius Chemisch-Pharmazeutisch Industrie Kg, Apparatebau Kg Artificial endocrinal gland
US4258717A (en) * 1977-09-06 1981-03-31 Institute Of Critical Care Medicine Vascular interface
US4638811A (en) * 1977-09-06 1987-01-27 Institute Of Critical Care Medicine Vascular interface
JPS54135474A (en) * 1978-02-17 1979-10-20 Radiometer As Method of and device for monitoring ph value of blood plasam in living body
US4384586A (en) * 1978-02-17 1983-05-24 Christiansen Torben F Method and apparatus for pH recording
US4240438A (en) * 1978-10-02 1980-12-23 Wisconsin Alumni Research Foundation Method for monitoring blood glucose levels and elements
US4717548A (en) * 1980-06-09 1988-01-05 The United States Of America As Represented By The Secretary Of The Department Of Health And Human Services Analytically controlled blood perfusion system
US4316466A (en) * 1980-06-27 1982-02-23 Biomedics, Inc. Body fluid drainage device
US4615340A (en) * 1985-02-27 1986-10-07 Becton, Dickinson And Company Sensor assembly suitable for blood gas analysis and the like and the method of use
EP0389719A2 (de) * 1989-03-27 1990-10-03 International Technidyne Corp System zur Aufnahme und Abgabe flüssiger Proben und speziell an die Körperflüssigkeitsprobenahme angepasste Methode
EP0389719A3 (de) * 1989-03-27 1991-03-20 International Technidyne Corp System zur Aufnahme und Abgabe flüssiger Proben und speziell an die Körperflüssigkeitsprobenahme angepasste Methode
US5533512A (en) * 1994-03-18 1996-07-09 Ohmeda Inc. Method and apparatus for detection of venous air emboli
US5758643A (en) * 1996-07-29 1998-06-02 Via Medical Corporation Method and apparatus for monitoring blood chemistry
US8626257B2 (en) 2003-08-01 2014-01-07 Dexcom, Inc. Analyte sensor
US8886273B2 (en) 2003-08-01 2014-11-11 Dexcom, Inc. Analyte sensor
US10052055B2 (en) 2003-08-01 2018-08-21 Dexcom, Inc. Analyte sensor
US11000215B1 (en) 2003-12-05 2021-05-11 Dexcom, Inc. Analyte sensor
US11020031B1 (en) 2003-12-05 2021-06-01 Dexcom, Inc. Analyte sensor
US8287453B2 (en) 2003-12-05 2012-10-16 Dexcom, Inc. Analyte sensor
US11633133B2 (en) 2003-12-05 2023-04-25 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8425417B2 (en) 2003-12-05 2013-04-23 Dexcom, Inc. Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion device
US11246990B2 (en) 2004-02-26 2022-02-15 Dexcom, Inc. Integrated delivery device for continuous glucose sensor
US10966609B2 (en) 2004-02-26 2021-04-06 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US10835672B2 (en) 2004-02-26 2020-11-17 Dexcom, Inc. Integrated insulin delivery system with continuous glucose sensor
US12102410B2 (en) 2004-02-26 2024-10-01 Dexcom, Inc Integrated medicament delivery device for use with continuous analyte sensor
US12115357B2 (en) 2004-02-26 2024-10-15 Dexcom, Inc. Integrated delivery device for continuous glucose sensor
US10932700B2 (en) 2004-07-13 2021-03-02 Dexcom, Inc. Analyte sensor
US10980452B2 (en) 2004-07-13 2021-04-20 Dexcom, Inc. Analyte sensor
US10827956B2 (en) 2004-07-13 2020-11-10 Dexcom, Inc. Analyte sensor
US10813576B2 (en) 2004-07-13 2020-10-27 Dexcom, Inc. Analyte sensor
US11883164B2 (en) 2004-07-13 2024-01-30 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US11064917B2 (en) 2004-07-13 2021-07-20 Dexcom, Inc. Analyte sensor
US7885697B2 (en) 2004-07-13 2011-02-08 Dexcom, Inc. Transcutaneous analyte sensor
US10799158B2 (en) 2004-07-13 2020-10-13 Dexcom, Inc. Analyte sensor
US11045120B2 (en) 2004-07-13 2021-06-29 Dexcom, Inc. Analyte sensor
US11026605B1 (en) 2004-07-13 2021-06-08 Dexcom, Inc. Analyte sensor
US10799159B2 (en) 2004-07-13 2020-10-13 Dexcom, Inc. Analyte sensor
US10993641B2 (en) 2004-07-13 2021-05-04 Dexcom, Inc. Analyte sensor
US10993642B2 (en) 2004-07-13 2021-05-04 Dexcom, Inc. Analyte sensor
US10524703B2 (en) 2004-07-13 2020-01-07 Dexcom, Inc. Transcutaneous analyte sensor
US7857760B2 (en) 2004-07-13 2010-12-28 Dexcom, Inc. Analyte sensor
US10722152B2 (en) 2004-07-13 2020-07-28 Dexcom, Inc. Analyte sensor
US8750955B2 (en) 2004-07-13 2014-06-10 Dexcom, Inc. Analyte sensor
US10709362B2 (en) 2004-07-13 2020-07-14 Dexcom, Inc. Analyte sensor
US8792953B2 (en) 2004-07-13 2014-07-29 Dexcom, Inc. Transcutaneous analyte sensor
US8812072B2 (en) 2004-07-13 2014-08-19 Dexcom, Inc. Transcutaneous medical device with variable stiffness
US7783333B2 (en) 2004-07-13 2010-08-24 Dexcom, Inc. Transcutaneous medical device with variable stiffness
US10918314B2 (en) 2004-07-13 2021-02-16 Dexcom, Inc. Analyte sensor
US9414777B2 (en) 2004-07-13 2016-08-16 Dexcom, Inc. Transcutaneous analyte sensor
US7640048B2 (en) 2004-07-13 2009-12-29 Dexcom, Inc. Analyte sensor
US10918313B2 (en) 2004-07-13 2021-02-16 Dexcom, Inc. Analyte sensor
US9986942B2 (en) 2004-07-13 2018-06-05 Dexcom, Inc. Analyte sensor
US10709363B2 (en) 2004-07-13 2020-07-14 Dexcom, Inc. Analyte sensor
US10918315B2 (en) 2004-07-13 2021-02-16 Dexcom, Inc. Analyte sensor
US10918316B2 (en) 2005-03-10 2021-02-16 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10898114B2 (en) 2005-03-10 2021-01-26 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10856787B2 (en) 2005-03-10 2020-12-08 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10610137B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10610136B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10610135B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10617336B2 (en) 2005-03-10 2020-04-14 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10709364B2 (en) 2005-03-10 2020-07-14 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10918317B2 (en) 2005-03-10 2021-02-16 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10918318B2 (en) 2005-03-10 2021-02-16 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10716498B2 (en) 2005-03-10 2020-07-21 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10925524B2 (en) 2005-03-10 2021-02-23 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10743801B2 (en) 2005-03-10 2020-08-18 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US11000213B2 (en) 2005-03-10 2021-05-11 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US11051726B2 (en) 2005-03-10 2021-07-06 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10813577B2 (en) 2005-06-21 2020-10-27 Dexcom, Inc. Analyte sensor
US7367942B2 (en) * 2006-02-02 2008-05-06 Palco Labs, Inc. Method and apparatus for testing blood glucose in a reversible infusion line
US20070179437A1 (en) * 2006-02-02 2007-08-02 Henry Grage Method and apparatus for testing blood glucose in a reversible infusion line
US8911367B2 (en) 2006-10-04 2014-12-16 Dexcom, Inc. Analyte sensor
US8449464B2 (en) 2006-10-04 2013-05-28 Dexcom, Inc. Analyte sensor
US8298142B2 (en) 2006-10-04 2012-10-30 Dexcom, Inc. Analyte sensor
US10349873B2 (en) 2006-10-04 2019-07-16 Dexcom, Inc. Analyte sensor
US7775975B2 (en) 2006-10-04 2010-08-17 Dexcom, Inc. Analyte sensor
US8364230B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US9451908B2 (en) 2006-10-04 2016-09-27 Dexcom, Inc. Analyte sensor
US8275438B2 (en) 2006-10-04 2012-09-25 Dexcom, Inc. Analyte sensor
US8774886B2 (en) 2006-10-04 2014-07-08 Dexcom, Inc. Analyte sensor
US8364231B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US7615007B2 (en) 2006-10-04 2009-11-10 Dexcom, Inc. Analyte sensor
US20080119703A1 (en) * 2006-10-04 2008-05-22 Mark Brister Analyte sensor
US11399745B2 (en) 2006-10-04 2022-08-02 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US11382539B2 (en) 2006-10-04 2022-07-12 Dexcom, Inc. Analyte sensor
US8562528B2 (en) 2006-10-04 2013-10-22 Dexcom, Inc. Analyte sensor
US8532730B2 (en) 2006-10-04 2013-09-10 Dexcom, Inc. Analyte sensor
US8478377B2 (en) 2006-10-04 2013-07-02 Dexcom, Inc. Analyte sensor
US20080119704A1 (en) * 2006-10-04 2008-05-22 Mark Brister Analyte sensor
US20080119706A1 (en) * 2006-10-04 2008-05-22 Mark Brister Analyte sensor
US8425416B2 (en) 2006-10-04 2013-04-23 Dexcom, Inc. Analyte sensor
US8447376B2 (en) 2006-10-04 2013-05-21 Dexcom, Inc. Analyte sensor
US11373347B2 (en) 2007-06-08 2022-06-28 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US20080306434A1 (en) * 2007-06-08 2008-12-11 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US10403012B2 (en) 2007-06-08 2019-09-03 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US9741139B2 (en) 2007-06-08 2017-08-22 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US8562558B2 (en) 2007-06-08 2013-10-22 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US20080306444A1 (en) * 2007-06-08 2008-12-11 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US11160926B1 (en) 2007-10-09 2021-11-02 Dexcom, Inc. Pre-connected analyte sensors
US11744943B2 (en) 2007-10-09 2023-09-05 Dexcom, Inc. Integrated insulin delivery system with continuous glucose sensor
US8396528B2 (en) 2008-03-25 2013-03-12 Dexcom, Inc. Analyte sensor
US10602968B2 (en) 2008-03-25 2020-03-31 Dexcom, Inc. Analyte sensor
US11896374B2 (en) 2008-03-25 2024-02-13 Dexcom, Inc. Analyte sensor
US10980461B2 (en) 2008-11-07 2021-04-20 Dexcom, Inc. Advanced analyte sensor calibration and error detection
WO2014015691A1 (zh) * 2012-07-20 2014-01-30 深圳市麦迪聪医疗电子有限公司 一种血气分析仪及其使用方法
US11382540B2 (en) 2017-10-24 2022-07-12 Dexcom, Inc. Pre-connected analyte sensors
US11706876B2 (en) 2017-10-24 2023-07-18 Dexcom, Inc. Pre-connected analyte sensors
US11943876B2 (en) 2017-10-24 2024-03-26 Dexcom, Inc. Pre-connected analyte sensors
US11350862B2 (en) 2017-10-24 2022-06-07 Dexcom, Inc. Pre-connected analyte sensors
US11331022B2 (en) 2017-10-24 2022-05-17 Dexcom, Inc. Pre-connected analyte sensors
US11416397B2 (en) * 2019-10-14 2022-08-16 Intel Corporation Global persistent flush

Also Published As

Publication number Publication date
GB1463675A (en) 1977-02-02
JPS507391A (de) 1975-01-25
DE2365048A1 (de) 1974-08-15
JPS5649575B2 (de) 1981-11-24
FR2212940A5 (de) 1974-07-26

Similar Documents

Publication Publication Date Title
US3838682A (en) Automated blood analysis system
US4109505A (en) Automated blood analysis system
US3910256A (en) Automated blood analysis system
US6080583A (en) Blood analysis system and method for regulating same
US6017318A (en) Feedback controlled drug delivery system
AU697232B2 (en) In situ calibration system for sensors located in a physiologic line
KR101254530B1 (ko) 복막 투석 치료용 휴대용 장치
CA1328359C (en) Fluid sample collection and delivery system and methods particularly adapted for body fluid sampling
US5134079A (en) Fluid sample collection and delivery system and methods particularly adapted for body fluid sampling
US4796644A (en) Apparatus for infusion and removal of samples of blood and other body fluids
US4127111A (en) Automatic blood sampling system and method
US4535786A (en) Measurement of body fluid chemistry
US7608042B2 (en) Blood monitoring system
US3997420A (en) Automatic analyzer
US20070191716A1 (en) Blood monitoring system
US20100020309A1 (en) Blood monitoring system
JPH1062434A (ja) 体液の分析装置
JP2002534227A (ja) 液体の投与のための注入器
JP6998444B2 (ja) 血液凝固検査システムおよび血液凝固検査システムの制御方法
CN109557295A (zh) 血气测试方法、血气测试主机、试剂包以及血气测试卡
CN100488444C (zh) 微分析系统
JPH0339696B2 (de)
US20230313108A1 (en) Sampling Device And Cell Culture System
SG172305A1 (en) Device for measuring at least one parameter of an arterial blood sample
JPH03118470A (ja) 血液分析装置