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WO2007133942A2 - Purge d'air dans un système d'injection de fluide - Google Patents

Purge d'air dans un système d'injection de fluide Download PDF

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Publication number
WO2007133942A2
WO2007133942A2 PCT/US2007/067982 US2007067982W WO2007133942A2 WO 2007133942 A2 WO2007133942 A2 WO 2007133942A2 US 2007067982 W US2007067982 W US 2007067982W WO 2007133942 A2 WO2007133942 A2 WO 2007133942A2
Authority
WO
WIPO (PCT)
Prior art keywords
fluid
drive mechanism
pressurizing unit
syringe
injection
Prior art date
Application number
PCT/US2007/067982
Other languages
English (en)
Other versions
WO2007133942A3 (fr
Inventor
Alan Evans
Sidney D. Nystrom
Original Assignee
Acist Medical System, Inc.
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 Acist Medical System, Inc. filed Critical Acist Medical System, Inc.
Publication of WO2007133942A2 publication Critical patent/WO2007133942A2/fr
Publication of WO2007133942A3 publication Critical patent/WO2007133942A3/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/14212—Pumping with an aspiration and an expulsion action
    • A61M5/14216—Reciprocating piston type
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/172—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body electrical or electronic
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/36—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests with means for eliminating or preventing injection or infusion of air into body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M2005/1401—Functional features
    • A61M2005/1403—Flushing or purging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2209/00—Ancillary equipment
    • A61M2209/01—Remote controllers for specific apparatus
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/007—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests for contrast media
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/14212—Pumping with an aspiration and an expulsion action
    • A61M5/14232—Roller pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16804—Flow controllers
    • A61M5/16827—Flow controllers controlling delivery of multiple fluids, e.g. sequencing, mixing or via separate flow-paths

Definitions

  • This application relates generally to an injector system for injecting medical fluids, such as radiographic contrast fluids.
  • Certain medical procedures are used in the diagnosis and treatment of cardiovascular conditions including abnormalities or restrictions in blood vessels.
  • a radiographic contrast material is injected through a catheter into a vein or artery, which then passes to vascular structures in fluid communication with the vein or artery.
  • X-rays are passed through the region of the body into which the contrast material is injected, they are absorbed by the contrast material, providing radiographic images of the desired vascular structure(s).
  • the images can be recorded on film or video tape and/or displayed on a fluoroscope monitor.
  • the images can be used for many purposes, as for example, diagnostics and for therapeutic procedures such as angioplasty, wherein a balloon is inserted into a vascular system and inflated to open a stenosis.
  • the contrast material can be injected into the catheter by either manual or automated injection systems. While the apparatus for injecting the contrast material can vary, most current systems include a syringe operatively connected with the catheter.
  • the syringe has a chamber for holding the contrast material and a plunger reciprocally moveable within the chamber.
  • the contrast material is suctioned into the chamber when the plunger is moved to create a partial vacuum within the chamber.
  • a reversal of the plunger direction first forces air out of the chamber and then delivers the contrast material to the catheter at a rate and volume determined by the speed of movement of the plunger.
  • air that is present in an injection syringe after a fill operation can purged back into a bottle containing the contrast material before a patient injection occurs.
  • part of the setup operation for a fluid injection system typically involves filling an injection syringe with contrast material.
  • a small amount of air may also be pulled into the syringe during the fill procedure. If this occurs, this small amount of air should be removed before performing a contrast material injection.
  • One embodiment provides a method to purge air from a pressurizing unit that is used in a powered fluid injection system.
  • the method includes moving a drive mechanism in a forward direction to an extended position within a pressurizing unit, retracting the drive mechanism in a rearward direction to partially fill the pressurizing unit with a first quantity of medical fluid, moving the drive mechanism in the forward direction to remove air from the pressurizing unit, and retracting the drive mechanism in the rearward direction to fill the pressurizing unit with a second quantity of fluid, the second quantity of fluid being greater than the first quantity of fluid.
  • a specified sequence and timing of operations optimally fills the syringe, removes air bubbles, maintains a low pressure in the contrast bottle, and makes the system available for injections in a short amount of time.
  • FIG. 1 is a perspective view illustrating a preferred embodiment of an angiographic injector system.
  • FIGS. 2A-2G are diagrams illustrating operations of the system of FIG. 1.
  • FIG. 3 is an electrical block diagram of the control system of the injector system of FIG. 1.
  • FIG. 4 illustrates front panel controls and displays of a preferred embodiment of the injector system.
  • FIGS. 5A and 5B are side and partial top perspective views of the remote control of the system of FIG. 1.
  • FIG. 6 is a perspective view of a foot operated remote control.
  • FIGS. 7A-7D illustrate the operation of the inlet check valve and manifold during contrast fill, air purge, and patient inject operations.
  • FIGS. 8A-8C illustrate operation of the inlet check valve in greater detail.
  • FIGS. 9 A and 9B are perspective views illustrating a second embodiment configuration of an angiographic injector system.
  • FIG. 10 is a mechanical block diagram illustrating the mounting configuration of the portions of the system disclosed in FIG. 9.
  • FIGS. 1 IA and 1 IB are an electrical block diagram of the control system and electrical functions of the system of FIGS. 9 and 10.
  • FIG. 12 is an electrical block diagram of the injector motor control portion of the control system of FIG. 11.
  • FIG. 13 is an electrical block diagram of the safety circuits associated with the peristaltic pump motor control portion of the control system of FIG. 11.
  • FIG. 14 is an illustration of a Power Up screen of the display of the system of FIG. 11.
  • FIG. 15 is an illustration of a Back Calibration screen of the display of the system of FIG. 11.
  • FIG. 16 is an illustration of a Check Screen screen of the display of the system of
  • FIG. 17 is an illustration of a Forward Calibration screen of the display of the system of FIG. 11.
  • FIG. 18 is an illustration of a First Start-Up Instruction screen of the display of the system of FIG. i l.
  • FIG. 19 is an illustration of a Second Start-Up Instruction screen of the display of the system of FIG. 11.
  • FIG. 20 is an illustration of a Third Start-Up Instruction screen of the display of the system of FIG. 11.
  • FIG. 21 is an illustration of a Fourth Start-Up Instruction screen of the display of the system of FIG. 11.
  • FIG. 22 is an illustration of a Ready to Fill Syringe screen of the display of the system of FIG. 11.
  • FIG. 23 is an illustration of a Syringe Filling Notice screen of the display of the system ofFIG. i l.
  • FIG. 24 is an illustration of a Purging Notice screen of the display of the system of FIG. 11.
  • FIG. 25 is an illustration of a Line Purge Instruction screen of the display of the system of FIG. 11.
  • FIG. 26 is an illustration of a Purging Line Notice screen of the display of the system of FIG. 11.
  • FIG. 27 is an illustration of a Final Saline Flush Instruction screen of the display of the system of FIG. 11.
  • FIG. 28 is an illustration of a Saline Flushing Notice screen of the display of the system ofFIG. i l.
  • FIG. 29 is an illustration of a Final Start-Up screen of the display of the system of FIG. 11.
  • FIG. 30 is an illustration of the MAIN display screen of the system of FIG. 11.
  • FIG. 31 is an illustration of tahe MAIN display screen of FIG. 30 illustrating operation in an injecting mode.
  • FIG. 32 is an illustration of the MAIN display screen of FIG. 30 illustrating the keypad that is displayed when the Fixed Rate mode of operation is selected.
  • FIG. 33 is an illustration of the MAIN display screen of FIG. 30 illustrating the keypad that is displayed when the Variable Rate mode of operation is selected.
  • FIG. 34 is an illustration of the MAIN display screen of FIG. 30, illustrating operation in a Manual Purging mode.
  • FIG. 35 is an illustration of the MAIN display screen of FIG. 30, illustrating operation in a Manual Refilling mode.
  • FIGS. 36A-C illustrate comparative graphs for default injection parameter values for Flow Rate Limits determined by algorithms relating to patient weight.
  • FIGS. 37A-C illustrate comparative graphs for default injection parameter values for Volume Limits determined by algorithms relating to patient weight.
  • FIG. 38 is a diagrammatic flow chart illustrating the process used to determine the patient related default injection parameters of FIGS. 36 and 37.
  • FIG. 39 is a block diagram of one embodiment of a powered injection system, according to one embodiment.
  • FIG. 40 is a block diagram of an alternate embodiment of a powered injection system.
  • FIG. 41 is a flow diagram of a method for purging air bubbles, according to one embodiment.
  • FIG. 1 shows an injector system 10 for injecting radiographic contrast material into a blood vessel under interactive physician control.
  • System 10 includes main console 12, hand held remote control 14, syringe holder 16, syringe body 18, syringe plunger 20, radiographic material reservoir (bottle) 22, one-way valve 24, manifold 26, high pressure tube 28, catheter 30, patient medication port 32, three-way stop-cock 34, T-connector 36, pressure transducer 38, stop-cock 40, tubing 42, peristaltic pump 44, saline check valve 46, waste check valve 48, saline bag 50, waste bag 52, and bag support rack 54.
  • Console 12 houses the electrical controls for system 10, together with the motors which drive piston 20 and peristaltic pump 44.
  • user interface 55 provides control switches 56 and display 58 through which the user may enter control settings and monitor the operational state of system 10.
  • the console can be free-standing, preferably configured for mounting on a transport cart assembly.
  • Remote control 14 is connected to console 12 by cable 60 (although in other embodiments remote control 14 may be connected by a wireless connection such as an RF, infrared optic, or ultrasonic link).
  • Remote control 14 is, in the embodiment shown in FIG. 1, a hand-held control which includes reset and saline push button switches 62 and 64, respectively, and flow rate control lever or trigger 66. By squeezing trigger 66, the user can provide a command signal to console 12 to provide a continuously variable injection rate.
  • Syringe holder 16 projects from the left hand side of console 12.
  • Syringe holder 16 is preferably a clear material, and includes a half cylindrical back shell 68, a half cylindrical front door 70 (which is shown in open position in FIG. 1), and reservoir holder 72.
  • Syringe 18 is a transparent or translucent plastic cylinder having its open end 74 connected to console 12. Closed end 76 of syringe 18 contains two ports: upper port 78 and lower port 80.
  • Plunger 20 is movable within syringe body 18. Plunger 20 is connected to, and driven by a motor located within console 12. Radiographic contrast material reservoir 22 is connected through one-way check valve 24 to upper port 78. Radiographic contrast material is drawn from reservoir 22 through check valve 24 and upper port 78 into the pumping chamber defined by syringe body 18 and plunger 20.
  • Check valve 24 is preferably a weighted one-way valve which permits air to flow from syringe body 18 back into reservoir 22, but will not permit radiographic contrast material to flow from syringe body 18 to reservoir 22. This permits automatic purging of air from the system, as will be described in more detail later.
  • Lower port 80 of syringe body 18 is connected to manifold 26.
  • Manifold 26 includes a spring biased spool valve which normally connects transducer/saline port 82 and patient port 84. When radiographic contrast material is to be injected, the pressure of the radiographic material causes the spool valve to change states so that lower port 80 is connected to patient port 84.
  • High pressure tube 28 is a flexible tube which connects patient port 84 to catheter 30.
  • Three-way stop-cock 34 is located at the distal end of tube 28.
  • Rotatable luer lock connector 86 is connected to stop-cock 34 and mates with luer connector 88 at the proximal end of catheter 30.
  • Stopcock 34 either blocks flow between tube 28 and catheter 30, permits flow, or connects medication port 32 to catheter 30.
  • system 10 also permits other related functions to be performed.
  • a device for delivering the patient medication (not shown in FIG. 1) may be connected to medication port 32 when medication is to be delivered through catheter 30 to the patient.
  • pressure transducer 38 monitors the blood pressure through the column of fluid which extends from catheter 30, tube 28, patient port 84, manifold 26, transducer/saline port 82, tubing 90, T-connector 36, and tubing 92.
  • Transducer 38 has an associated stop-cock 40 which allows transducer 38 to be exposed to atmospheric pressure during calibration and also allows for removal/expulsion of trapped air so the dome chamber of transducer 38 can be flushed with saline.
  • Peristaltic pump 44 supplies saline solution from bag 50 through saline check valve 46, tubing 42, T-connector 36 and tubing 90 to saline port 82.
  • peristaltic pump 44 When peristaltic pump 44 is operating to supply saline solution, the saline solution is supplied through manifold 26 to patient port 84 and then through tube 28 to catheter 30.
  • Peristaltic pump 44 also operates in an opposite direction to draw fluid from catheter 30 and through tube 28, manifold 26, tubing 90, T-connector 36 and tubing 42 to waste check valve 48 and then into waste collection bag 52.
  • syringe body 18, manifold 26, tube 28, catheter 30, T-connector 36, tubing 42, check valves 46 and 48, bags 50 and 52, and tubing 90 and 92 are all disposable items. They must be installed in system 10 each time an angiography procedure is to be performed with a new patient. Once system 10 is set up with all the disposable items installed, door 70 is closed, and syringe body 18 filled with contrast material and purged of air, the user (typically a physician) enters into system 10 the safety parameters that will apply to the injection of radiographic contrast material.
  • safety parameters typically include the maximum amount of radiographic contrast material to be injected during any one injection, the maximum flow rate of the injection, the maximum pressure developed within syringe body 18, and the maximum rise time or acceleration of the injection.
  • the user operates remote control 14 by squeezing trigger 66.
  • system 10 causes the flow rate of the injection to increase as the force or distance of travel of trigger 66 is increased.
  • System 10 allows the user to tailor the contrast injections to the needs of the patient, thereby maximizing the quality of the procedure, increasing the safety, and reducing the amount of contrast material required to perform the fluoroscopic examination.
  • FIGS. 2A-2G are diagrams illustrating fluid flow paths during seven different operations of system 10. Those operational are contrast fill (FIG. 2A), air purge (FIG. 2B), patient inject (FIG. 2C), patient pressure (FIG. 2D), saline flush (FIG. 2E), aspirate waste (FIG. 2F), and medicate patient (FIG. 2G).
  • FIGS. 2A-2G are diagrams illustrating fluid flow paths during seven different operations of system 10. Those operational are contrast fill (FIG. 2A), air purge (FIG. 2B), patient inject (FIG. 2C), patient pressure (FIG. 2D), saline flush (FIG. 2E), aspirate waste (FIG. 2F), and medicate patient (FIG. 2G).
  • the contrast fill operation illustrated in FIG. 2A involves the filling of syringe body 18 with radiographic contrast material from reservoir (contrast media supply) 22.
  • the contrast fill operation is performed during initial set up of system 10, and may be repeated during operation of system 10 whenever syringe body 18 is running low on radiographic contrast material.
  • plunger 20 is initially driven to its furthest forward position adjacent closed end 76 of syringe body 18. This will expel to the atmosphere the majority of the air which is located within syringe body 18.
  • Plunger 20 is then retracted, which creates a vacuum within syringe body 18 which draws contrast material from reservoir 22 through check valve 24 into syringe body 18 through upper port 78.
  • the Contrast Fill operation typically will result in some air being drawn into or remaining within syringe body 18. It is important, of course, to prevent air from being injected into the patient through catheter 30. That is the purpose of the Air Purge operation shown in FIG. 2B. Also, the location of two ports at different elevations allows for a greater amount of safety in preventing air bubbles in the injection.
  • plunger 20 travels forward to expel trapped air within syringe body 18.
  • the air being lighter than the contrast material, gathers near the top of syringe body 18.
  • one-way valve 24 is a weighted one-way valve which allows flow of radiographic contrast material from reservoir 22 to upper port 78, but will not allow radiographic contrast material to flow in the opposite direction from upper port 78 to reservoir 22.
  • Valve 24 will, however, allow air to flow from port 78 to reservoir 22.
  • valve 24 closes to prevent any further flow toward reservoir 22.
  • Valve 24 can also, in alternative embodiments, can be a solenoid actuated or motor driven valve operated under control of the electric circuitry within console 12. In either case, valve 24 is capable to withstanding the relatively high pressures to which it will be subjected during the inject operation. Preferably, valve 24 is capable of withstanding static fluid pressures up to about 1200 p.s.i.
  • FIG. 2C illustrates the Patient Inject operation.
  • Plunger 20 travels forward under the interactive control of the user, who is controlling trigger 66 of remote control 14.
  • the movement of Plunger 20 creates hydraulic pressure to force contrast material out of syringe body 18 through lower port 80 and through manifold 26 and high pressure tube 28 into catheter 30.
  • syringe lower port 80 and patient port 84 are connected for fluid flow during the patient inject operation.
  • Manifold 26 contains a valve which controls the routing of fluid connections between patient port 84 and either syringe bottom port 80 or transducer/saline port 82.
  • manifold 26 includes a spool valve which is spring biased so that patient port 84 is normally connected to transducer/saline port 82 (as illustrated in FIGS. 2A and 2B).
  • a spool valve which is spring biased so that patient port 84 is normally connected to transducer/saline port 82 (as illustrated in FIGS. 2A and 2B).
  • the spool valve opens automatically during the patient inject operation in response to increase pressure exerted on it from the syringe lower port 80.
  • the spool valve closes and returns to its original position allowing for connection of patient port 84 to transducer 38 when a slight vacuum is applied by retraction of plunger 20 at the end of each Patient Inject operation
  • the valve within manifold 26 is an electromechanical or motor driven valve which is actuated at appropriate times to connect either syringe lower port 80 or transducer/saline port 82 to patient port 84, The actuator mechanism is controlled by console 12. Once again in this alternative embodiment, the valve protects pressure transducer 38 from being exposed to high pressure.
  • FIG. 2D illustrates the Patient Pressure operation.
  • System 10 allows for reading of the patient's blood pressure, which is monitored through catheter 30.
  • Patient blood pressure can be monitored through the use of pressure transducer 38, at any time except during the patient inject, saline flush, and waste aspirate operations.
  • the pressure reading being produced by pressure transducer 38 may be normalized by manually opening stopcock 40 and closing stop-cock 34 to expose pressure transducer 38 to atmospheric pressure.
  • saline solution is used to flush all of the internal lines, pressure transducer chamber 38, tube 28, and catheter 30. As shown in FIG.
  • peristaltic pump 44 is operating in a direction which causes saline solution to be drawn from bag 50 through check valve 46 and through tubing 42 to saline port 82.
  • Manifold 26 connects saline port 82 to patient port 84 so that saline solution is pumped out of patient port 84 and through tube 28 and catheter 30.
  • patient port 84 is again connected to saline port 82.
  • peristaltic pump 44 is operating in the opposite direction from its rotation during the saline flush operation.
  • patient fluids are aspirated from patient port 84 to saline port 82 and then through tubing 42 and check valve 48 into waste collection bag 52.
  • Peristaltic pump 44 acts as a valve pinching/occluding tubing 42 and preventing back flow to/from saline and waste containers 50 and 52 in conjunction with check valves 46 and 48.
  • System 10 allows for that option by providing patient medication port 32. As shown in FIG. 2G, when stop-cock 34 is open, a medication source connected to port 32 will be connected to patient port 84, and thereby to catheter 30. During the medicate patient operation, peristaltic pump 44 and plunger 20 are not moving.
  • FIG. 3 is an electrical block diagram of a control system that has been used with above-described angiographic injector system.
  • the electrical control system of FIG. 3 includes a single digital computer 100, which receives input signals from remote control 14 and front panel controls 56 through interface 102, and provides signals to display 58 to display operation data, alerts, status information and operator prompts.
  • a subsequent preferred embodiment will describe an improved electrical control system; however the single computer system is being described herein to complete the functional description of an angiographic injector system that incorporates the components of the angiographic injector system 10 described above.
  • Computer 100 controls the motion of plunger 20 through a motor drive circuit which includes motor 104, motor amplifier 106, tachometer 108, potentiometer 110, a rectifier 112, pressure sensing load cell 114, and A/D converter 116.
  • Motor amplifier 106 provides a Drive 1 signal to motor 104 in response to Control
  • the outputs of tachometer 108 and potentiometer 110 are supplied to computer 100 through A/D converter 116 as Speed Monitor and Position Monitor signals. These allow computer 100 to check motor speed, motor direction, and position (volume is a calculated value).
  • Pressure sensor 114 senses motor current or plunger force in order to measure the pressure being applied to the radiographic contrast material within syringe body 18.
  • This Pressure Monitor Signal is supplied through A/D converter 116 and interface 102 to computer 100.
  • Peristaltic pump 44 is driven under the control of computer 100 through pump motor 120, motor driver 122 and optical encoder 124.
  • Computer 100 provides Saline (Forward) and Waste (Reverse) drive signals to motor driver 122 to operate pump motor 120 in a forward direction for saline flush and a reverse direction for waste aspiration.
  • Optical encoder 124 provides the Speed Direction Monitor signal to interface 102 which indicates both the speed and the direction of rotation of pump motor 120.
  • valve motor 130 is used to actuate valves such as one-way valve 24 and the valve within manifold 26.
  • computer 100 controls valve motor 130 through motor driver 132, and monitors position through a Position Monitor feedback signal from potentiometer 134.
  • valve motor 130 is a stepper motor
  • Computer 100 monitors temperature of the contrast material based upon a Temp Monitor signal from temperature sensor 140. Temperature sensor 140 is preferably positioned near syringe body 18. If the temperature being sensed by temperature sensor 140 is too high, computer 100 will disable operation motor 104 to discontinue patient injection. If the temperature is too low, computer 100 provides a/Temp Enable drive signal to heater drive 150, which energizes heater 152. In one preferred embodiment, heater 152 is a resistive film heater which is positioned within syringe holder 116 adjacent to syringe body 18.
  • Computer 100 also receives feedback signals from contrast bottle sensor 160, forward limit sensor 162, reverse limit sensor 164, syringe missing sensor 166, chamber open sensor 168, no contrast bubble detector 170, and air in line bubble detector 172.
  • Contrast bottle sensor 160 is a miniature switch located within reservoir holder 72. The state of the Contrast Bottle Present signal from sensor 160 indicates whether a reservoir 22 is in position within holder 72. If reservoir 22 is not present, computer 100 will disable the fill operation.
  • Forward limit and reverse limit sensors 162 and 164 sense the end limit positions of plunger 20. When plunger 20 reaches its forward limit position, no further forward movement of plunger 20 is permitted. Similarly, when reverse limit sensor 164 indicates that plunger 20 has reached its reverse limit position, no further reverse movements are permitted.
  • Syringe missing sensor 166 is a miniature switch or infrared emitter/detector which indicates when syringe body 18 is not in position within syringe holder 16. If syringe body 18 is not in position, all movement functions are disabled except that plunger 20 can move to its reverse limit position (i.e., return to zero).
  • Chamber open sensor 168 is a miniature switch or infrared emitter/detector which senses when door 70 of syringe holder 16 is open. When the signal from sensor 168 indicates that door 70 is open, all movement functions are disabled. Only when door 70 is closed and locked may any movement be allowed.
  • Bubble detector 170 is positioned between reservoir 22 and top port 78, and is preferably an infrared emitter/detector which senses air bubbles. If an air bubble is sensed in the flow path between reservoir 22 and top port 78 during a fill operation, the fill operation is disabled until a new reservoir is connected.
  • Bubble detector 172 is positioned to sense air bubbles in high pressure line 28. It is preferably an infrared emitter/detector type of bubble detector. Any air bubble which is sensed in high pressure line 28 results in the disabling of all fluid push out functions, whether the fluid is saline solution from peristaltic pump 44 or contrast material from syringe body 18.
  • the control system of FIG. 3 also includes the capability to provide a control signal to x-ray equipment through relay 180 which is controlled by computer 100.
  • computer 100 receives data from blood pressure transducer 38 and from an electrocardiograph (ECG) system, which is separate from injector system 10.
  • ECG electrocardiograph
  • the Pressure and ECG signals are received through signal conditioners and AfD converter 190, and are transferred to computer 100.
  • the ECG signal is used by computer 100 in one preferred embodiment, to synchronize operation of motor 104 (and thus the Patient Inject operation) with heart beats.
  • the injection of radiographic contrast material is synchronized to the coronary artery blood flow.
  • the time periods of systole and diastole are determined using an electrocardiographic (ECG) electrical signal, arterial blood pressure waveform analysis, or other timing based on the heart rate.
  • ECG electrocardiographic
  • the injection of contrast material is interrupted during the period of systole, which reduces or stops contrast injection during this time.
  • remote control 14 the operator can vary the rate of contrast injection into the coronary artery while computer 100 automatically pulses the contrast injection to the cardiac cycle.
  • a variable time offset can be entered through control panel 54 such that the timing of the cardiac cycle can be offset by a selected time. Since the magnitude of the phase lag may be dependent on the frequency of the heart rate, an algorithm within computer 100 continuously and automatically adjusts the magnitude of the time offset, based on the instantaneous heart rate during the injection of contrast material.
  • Front panel control switches 56 include Set Up/Fill/End switch 200, Purge switch 202, Aspirate switch 204, Saline switch 206, Enable OK switch 208, Injection Volume Limit switches 210a and 210b, Injection Flow Rate Limit switches 212a and 212b, Injection Pressure Limit switches 214a and 214b, Rise Time switches 216a and 216b OK switch 218, Injection Range Toggle switch 220, Large Injection OK switch 222, and Stop switch 224.
  • Set Up/Fill/End switch 200 is a momentary push button switch. When it is first activated, the user will be notified to place syringe 18 in syringe holder 16. When syringe 18 has been placed in syringe holder 16 (which is indicated to computer 100 by sensor 166), the user will be instructed to close and lock the chamber (i.e., to close door 70). Plunger 20 is moved to its full forward position expelling all air within the syringe. Display 58 then indicates to the operator that contrast reservoir 22 should be connected.
  • contrast reservoir 22 Once contrast reservoir 22 has been put in place, the operator is requested to depress OK switch 218, at which time plunger 20 will retract at a set rate (preferably corresponding to a flow rate of 10 ml per second) to the maximum syringe volume. If the real speed (as indicated by feedback to computer 100 from A/D converter 116) is greater than the set speed, system 10 will stop.
  • plunger 20 is at its rearward most position, motor 104 is actuated to move plunger 20 forward to purge all air bubbles.
  • Pressure sensor 114 provides an indication of when one-way valve 24 is closed and pressure is beginning to build up within syringe body 18. Once the purge is completed, the total volume injected and the number of injections counter is reset.
  • switch 200 also allows for Ml retraction and disengagement of plunger 20 from syringe body 18.
  • Purge switch 202 is a protected momentary push button switch. When activated,
  • Purge switch 202 causes plunger 20 to move forward to expel air through top port 78.
  • the forward movement of plunger 20 is limited and stopped when a predetermined pressure within syringe 18 is reached. This is sensed by pressure sensor 114.
  • the purge operation which is initiated by Purge switch 202 will expel air within syringe 20.
  • the user may also use Purge switch 202 to purge fluid through patient port 84 by depressing and holding Purge switch 202 continuously on.
  • Aspirate switch 204 is a momentary push button switch which causes computer
  • Pump motor 120 is operated to aspirate catheter 30 at a set speed, with the aspirated fluid being collected in waste bag 52. All other motion functions are disengaged during aspiration. If the real speed of motor 120 is greater than a set speed, computer 100 will stop motor 120.
  • Saline switch 206 is an alternate action switch. Pump motor 120 is activated in response to Saline switch 206 being pushed on, and saline solution from bag 50 is introduced into manifold 26 and catheter 30 at a set speed. If Saline switch 206 is not pushed a second time to stop the flow of saline solution within 10 seconds, computer 100 automatically stops pump motor 120. If a time-out is reached, Saline switch 206 must be reset to its original state prior to initiating any further actions.
  • Enable OK switch 208 is a momentary push button switch. After the system has detected a disabling function at the end of an injection other than a limit, Enable OK switch 208 must be activated prior to activating OK switch 218 and initiating any further function.
  • Injection Volume Limit keys 210a and 210b are pushed to either increase or decrease the maximum injection volume that the system will inject during any one injection. Key 210a causes an increase in the maximum volume value, and key 210b causes a decrease. Once the maximum injection volume limit has been set, if the measured volume reaches the set value, computer 100 will stop motor 104 and will not restart until OK switch 218 has been depressed. If a large injection (i.e., greater than 10 ml) has been selected, OK switch 218 and Large Injection OK switch 220 must both be reset prior to initiating the large injection.
  • Injection Flow Rate Limit keys 212a and 212b allow the physician to select the maximum flow rate that the system can reach during any one injection. If the measured rate (which is determined by the feedback signals from tachometer 108 and potentiometer 110) reaches the set value, computer 100 will control motor 104 to limit the flow rate to the set value.
  • Injection Pressure Limit keys 214a and 214b allow the physician to select the maximum pressure that the system can reach during any one injection. If the measured pressure, as determined by pressure sensor 114, reaches the set value, computer 100 will control motor 104 to limit the pressure to the injection pressure limit. The injection rate will also be limited as a result.
  • Rise Time keys 216a and 216b allow the physician to select the rise time that the system will allow while changing flow rate during any one injection.
  • Computer 100 controls motor 104 to limit the rise time to the set value.
  • keys 210a-210b, 212a-212b, 214a-214b, and 216a- 216b can be replaced by other devices for selecting numerical values. These include selector dials, numerical keypads, and touch screens.
  • OK switch 218 is a momentary push button switch which resets functions and hardware sensors. In response to OK switch 218 being activated, computer 100 controls display 58 to ask the operator to acknowledge that the correct function has been selected. Activation of OK switch 218 causes the status to be set to Ready.
  • Injection Range switch 220 is a toggle switch. Depending on whether switch 220 is in the "small” or “large” position, it selects either a high or a low injection volume range for the next injection.
  • Large Injection OK switch 222 is a momentary push button switch. When the large injection range has been selected by injection range switch 220, the Large Injection OK button 222 must be activated to enable OK switch 218. OK switch 218 must be activated prior to each injection. On large volume injections, the user is required to verify the volume selected by activating first Large Injection OK switch 222 and then OK switch 218.
  • Stop switch 224 is a momentary push button switch. When stop switch 224 is pushed, it disables all functions. Display 58 remains active.
  • Display panel 58 includes Set-Up display 250, Status display 252, Alerts display 254, Limits display 256, total number of injections display 260, total volume injection display 262, flow rate display 264, injection volume display 266, injection volume limit display 268, injection rate limit display 270, pressure limit display 272, rise time minimum display 274, large injection display 276, and real time clock display 278.
  • Set-Up display 250 contains a series of messages which are displayed as the operator goes through the set up procedure. The display of messages in set up display 250 are initiated by the actuation of set up switch 200 as described previously.
  • Status display 252 provides a flashing indication of one of several different operating conditions.
  • these status conditions which can be displayed include “Ready”, “Set-Up”, “Injecting”, “Filling”, “Flushing”, and "Aspirating”.
  • Alerts display 254 and Limits display 256 notify the operator of conditions in which system 10 has encountered a critical control parameter and will disable operation, or has reached an upper or lower limit and will continue to function in a limited fashion, or has reached an upper or lower limit and will continue to operate.
  • Total number of injections display 260 displays the total number of injections
  • Displays 264 and 266 provide information on the current or last injection.
  • Display 264 shows digital value of the real time flow rate to the patient during injection. Once the injection is completed, the value displayed on display 264 represents the peak flow rate reached during that injection.
  • Display 266 shows the digital value of the volume injected during the most recent injection.
  • Display 268 displays the digital value of the maximum injection volume selected by operation of switches 210a and 210b.
  • display 270 shows the digital value of the maximum flow rate that the system will allow, as selected by switches 212a and 212b.
  • Display 272 shows the digital value of the maximum pressure that the system will allow to be developed in syringe 18. The pressure limit is selected by switches 214a and 214b.
  • Display 274 displays the minimum rise time that the system will allow while changing flow rate. The minimum rise time is selected through switches 216a and 216b.
  • Large injection display 276 provides a clear indication when the large injection scale has been selected by the operator.
  • Real-time clock display 278 shows the current time in hours, minutes, and seconds.
  • FIGS. 5 A and 5 B show one embodiment of a remote control 14 which includes main housing 300, which is designed to conform to the users hand.
  • Trigger 66 is movable with respect to housing 300, and the position of trigger 66 generates a command signal which is a function of trigger position.
  • trigger 66 is linked to a potentiometer within housing 300.
  • the command signal controls the injunction flow rate or speed. The flow rate is directly proportional to trigger position.
  • Reset switch 62 is a momentary push button switch whose function is identical to that of OK switch 218. Alternatively, Reset switch 62 may also be labeled "OK".
  • Saline switch 64 on remote control 14 is an alternate action push button switch which is pushed to turn on and pushed again to turn off.
  • the function of Saline switch 62 is the same as that of Saline switch 206 on front panel 54.
  • Foot pedal remote control 14' in the form of a foot pedal is used instead of the hand held remote control 14 illustrated in FIG. 1 and in FIGS. 5A and 5B.
  • Foot pedal remote control 14' includes foot operated speed pedal or trigger 66' for providing a command signal, as well as Reset or OK switch 62' and Saline switch 64'. Covers 310 and 312 protect switches 62' and 64' so that they can only be actuated by hand and not accidentally by foot.
  • Foot pedal remote control 14' is connected to console 12 by cable 60', but could alternatively be connected by a wireless link.
  • FIGS. 7A-7D and FIGS. 8A- 8 C illustrate the construction and operation of one way valve 24 and manifold 26 during Contrast Fill, Air Purge and Patient Injection operation.
  • FIGS. 7A and 8A illustrate one way or check valve 24, manifold 26, syringe body
  • weighted ball 350 which is positioned at its lower seated position within valve chamber 352 in FIGS. 7A and 7B. Contrast material is being drawn into syringe body 18 by the rearward movement of plunger 20. The contrast material flows through passages 354 around ball 350 and into upper port 78.
  • Manifold 26 contains spring loaded spool valve 360, which includes spool body
  • bias spring 372 urges spool body 362 to its right-most position toward syringe body 18. In this position, spool body 362 blocks lower port 80 of syringe body 18 while connecting transducer saline port 82 to patient port 84 through diagonal passage 376.
  • O-rings 366 and 368 on the one hand, and O-ring 370 on the other hand, are positioned on the opposite sides of diagonal passage 376 to provide a fluid seal.
  • FIGS. 7B and 8B illustrate the Air Purge operation.
  • Syringe body 18 has been filled with contrast fluid, but also contains trapped air.
  • Plunger 20 is driven forward to force the air out of syringe body 18 through upper port 78 and through check valve 24.
  • Ball 350 is sufficiently heavy that the air being forced out of syringe body 18 and back toward reservoir 22 cannot lift ball 350 into its uppermost seated position where it would block the flow of air out of syringe body 18.
  • spool valve 360 is in the same position as in FIG.
  • Diagonal passage 376 connects transducer saline port 82 with patient port 84.
  • FIG. 7C and 8C illustrate the state of manifold 26 and check valve 24 at the end of the Air Purge operation and at the beginning of a Patient Inject operation.
  • Ball 350 may float on the radiographic contrast material, so that when all air has been removed and the radiographic contrast material begins to flow out of syringe body 18 and through upper port 78 to valve chamber 352, ball 350 is moved upwards to its upper seated position. Ball 350 blocks any continued upward flow of radiographic contrast material, as is illustrated in FIGS. 7C and 8C.
  • FIG. 7D illustrates the patient inject operation.
  • Plunger 20 is moving forward, and inlet check valve 24 is closed.
  • the pressure at lower port 80 has become sufficiently high to overcome the bias force of spring 372.
  • Spool body 362 has been driven to the left so that lower port 80 is connected to patient port 84.
  • spool body 362 blocks transducer/saline port 82.
  • spool valve 360 By virtue of the operation of spool valve 360, the high pressure generated by movement of plunger 20 and syringe body 18 is directly connected to patient port 84, while saline port 82 and pressure transducer 38 are protected from the high pressure.
  • the pressure to actuate may be variable and determined after manufacture by increasing or decreasing the syringe preload.
  • FIGS. 9a and 9b An alternative embodiment configuration of the angiographic injector system of the preceding figures is generally indicated at 10' in FIGS. 9a and 9b.
  • the physical locations of some of the components of the angiographic injector system 10 have been rearranged for facilitating use of the system.
  • the user interface 54, the control switches 56 and the display 58 of the first described embodiment have been consolidated into a single control panel 400.
  • the control panel 400 mounts to the console or injector head 12' on a swivel base that may be disconnected and reconnected by the user for optimal placement.
  • a mechanical diagrammatic chart of the FIG. 9 configuration is illustrated in FIG. 10.
  • the Power supply 59' circuits are illustrated as being mechanically mounted separate from the console 12'.
  • the console and power supply are mounted to a cart, generally indicated at 402 which includes wheels for easy movement and which is preferably designed to provide stability and deter tipping when used in its intended method.
  • the cart enables the console and power supply assemblies to be rapidly attached and detached for allowing docking of the console and power supply to a bed or other stationary device equipped with a mating connection device. Referring to FIG.
  • the hand controller 14' is illustrated as being operatively connected to the control panel 400, and the peristaltic pump assembly 44' is indicated as being mechanically mounted to the console 12'.
  • the assembly for holding the syringe and related components that have been previously described with regard to the first embodiment of the invention are generally indicated by the functional block entitled “mounting chamber” 404.
  • Those components previously described and referred to as "disposable" items i.e.: the syringe, the piston within the syringe body, the contrast valve, the patient manifold, the contrast spike and the patient blood pressure port
  • FIG. 11 An electrical functional block diagram of a second preferred control configuration for the angiographic injector system 10' is illustrated in FIG. 11.
  • the control system includes two separate computer systems, each having intelligence for monitoring and controlling functions of the injector system.
  • the computer system generally receives input signals from the control panel 400 and provides signals to display data, alerts, status information and operator prompts.
  • the computer system comprises two micro-computers.
  • a PC processor generally indicated at 410 acts as the master processor of the control system
  • an embedded processor generally indicated at 412, acts as the slave processor.
  • the master processor instructs the embedded processor to perform commands, but both processors monitor the actions taken. Both processors serve as independent monitors of action, for safety. Key functions such as the injector motor movement and peristaltic motor movement are monitored by both micro-computers.
  • the PC processor 410 has a 386 DOS central processing unit
  • the embedded core processor 412 has an HC 16 bit central processing unit. It will be appreciated that other types of microprocessors can be used. Referring to FIG. 11, it will be noted that PC processor 410 communicates with electrical components throughout the system by means of a first communication bus 414, and the embedded core processor 412 communicates with electrical circuits throughout the system by means of a second communication bus 416.
  • the two processors communicate with one another by means of their respective buses and a pair of communication registers generally indicated at 417 and 418.
  • General "watch dog/power fail/reset" functions are indicated by the functional block 419, and ECG acquired information can be collected on a first-in first-out basis by the functional block 420 for processing by both microprocessors.
  • the various electrical and sensing functions associated with the mounting chamber 404 include: a sensor entitled “chamber closed” (422) that indicates when the front loading chamber door used to load the disposable syringe into the mounting chamber is closed; a contrast bottle sensor indicated by “contrast empty” (423) which is located within the bottle holder and indicates whether fluid is present in the bottle; two valve sensors, indicated as “upper & lower valve sensors” (424) that are used by the computer to determine the state of the patient manifold valve and contrast valve; an electroluminescent back light, indicated by “EL backlight” (425) which facilitates manual bubble detection within the syringe and disposable items; a heating element, indicated by “contrast heater” (426) located inside the syringe holder adjacent to the syringe body; a pair of temperature sensors, indicated by "RTD Temp Sensor” (427) positioned near the syringe body for providing signals to control the contrast heater for maintaining the contrast material at a relatively constant temperature; and an air column
  • the control panel 400 includes an arm light 430, a speaker 431 , a touch screen 432, a display 433, and an emergency switch 434.
  • the arm light 430 is lit when the injector is ready to perform an injection.
  • the speaker 431 is an optional feature which can provide audible interface communication with the user.
  • the display 433 is in the preferred embodiment a liquid crystal (LCD) panel which is used to display the operational state of the system.
  • the touch screen 432 is overlayed on the LCD panel and is used by the user to control the system, as will be described in more detail hereinafter. All of the functions of the control panel communicate directly with the PC processor 410.
  • the emergency switch 434 communicates directly with both of the communication buses 414 and 416 as well as with cutoff relays and the injector motor solid state relay hereinafter described.
  • the hand control functional block 14' includes the circuit functions of the remote hand control unit.
  • the hand controller is a device used to control the angiographic injector pump in a manner such that when actuated by a user, outputs an electrical signal which is proportional to the displacement of the hand controlled device.
  • the controller is a passive electromechanical device that communicates with both of the microprocessors as indicated in FIG. 11.
  • the hand controller contains a pair of sealed on- contact sensors that can remotely determine position of an object and which are used to determine the active travel distance and placement of the hand movable portion of the controller.
  • the sensors are indicated by the two functional blocks indicated as “analog Hall effect” (440) and “digital Hall effect squeeze” (441).
  • the saline reset function is indicated by “saline reset button” (442), and the functional block indicated as “control type and connected” (443) provides for a setting indication through the hand controller to the microprocessors as to whether the system is being used to perform a "fixed rate” or "variable rate” injection. Under the variable rate mode of operation, the operator is allowed to vary the instantaneous injection rate by means of the hand controller up to a predetermined maximum flow rate.
  • the control system In the fixed mode of operation, when the operator squeezes the hand controller actuator, the control system will respond by simply injecting the contrast material at the predetermined fixed rate that has been entered into the control system prior to the injection procedure.
  • the peristaltic pump 44' is driven under the control of the microprocessors through a pump motor and motor driver.
  • the motor driver generally indicated by the "PWM control circuitry” (450) provides a pulse width modulated control signal to the peristaltic pump motor.
  • the computer provides both forward (Saline) and reverse (Waste) drive signals to the motor driver to operate the pump motor in a forward direction for a saline flush and in a reverse direction for waste aspiration.
  • the peristaltic pump of the preferred embodiment includes an "overspeed overtorque” sensor 451 and "cutoff relays” 452.
  • the overspeed/overtorque sensors 451 provide feedback signals to the microprocessors for accurately controlling the speed of the peristaltic pump by way of the pump drive circuits 450.
  • the cutoff relays 452 can be activated by either of the microprocessors or by the emergency stop switch 434.
  • the injector motor 460 is operatively connected to move the piston or wiper within the syringe and is controlled by a "motor controller” amplifier (461).
  • the motor driver 461 is an off-the-shelf servo amplifier which can be accurately controlled by means of a nested loop control configuration, hereinafter described.
  • the motor amplifier provides a drive signal to the motor in response to a control voltage.
  • Forward, reverse and break signals come from the computer, and a speed feedback signal from an optical encoder is used to control the speed.
  • Monitoring of the motor status is generally indicated by the functional block entitled “motor status overspeed/overtorque” (462) and an independent optical encoder sensor for sensing the motor speed and position, indicated by the “encoder” functional block (463).
  • a potentiometer is used to provide a back-up signal to the embedded microprocessor indicating the absolute "position" of the motor.
  • the potentiometer is indicated in the block diagram as the "absolute position pot.” functional block (464).
  • the outputs of the optical encoder and potentiometer are supplied to the processors as speed monitor and position monitor signals and allow the computers to check motor speed, motor direction and position.
  • a pair of forward and reverse limit sensors sense the end limit positions of the syringe piston and are indicated by the functional block entitled "F/R limit switches" (465). When the piston reaches its forward limit position, no further forward movement is permitted. Similarly, when the reverse limit sensor indicates that the piston has reached its reverse limit position, no further reverse movements are permitted.
  • the injector motor control also includes a solid state relay (470) for disabling the injector motor under command from either of the processors or the emergency switch 434.
  • the power supply 59' provides all electrical power to the system and includes an externally selectable voltage range switch 59a' enabling selection of connection of the power supply to either 110-120 volts AC or 220-240 volts AC.
  • the line voltage operating frequency must be between 47 and 63 Hz, and the line voltage must be capable of carrying ten amps of current.
  • the power supply further includes a power indicator light 59b' an on/off switch 59c' and a cable connector 59d' providing a connector for a cable leading to the circuits within the chassis 12'.
  • a more detailed electrical functional block circuit network for a preferred nested control loop configuration for control of the injector motor 460 is illustrated in FIG. 12.
  • the injector motor 460 is in the preferred embodiment, a brushless DC motor controlled by the servo amplifier network circuit 461.
  • the servo amplifier network 461 is a BE30A Series PWM Brushless Servo Amplifier model BE25A20 designated to drive a brushless DC motor at a high switching frequency.
  • the servo amplifier uses a quadrature encoder feedback input signal for velocity control.
  • the servo amplifier has an output drive port generally indicated at 461a, a feedback signal input port 461b, a speed control signal input port 461c and a pair of analog output signal ports 46 Id and, 46 Ie respectively.
  • the output port 46 Id carries a voltage signal developed within the servo amplifier that is proportional to the pressure or torque of the motor 460, and provides a signal to an output feedback line referred to as the "Analog Current" line.
  • the output port 46 Ie carries a voltage signal developed within the servo amplifier that is proportional to the speed of the motor 460, and provides a signal to the line indicated as "Analog Speed”.
  • An optical quadrature encoder (not illustrated in FIG. 12) is operatively connected to the output drive of the injector motor 460 (and indicated at 463 in FIG. 11), provides a pulse train feedback signal back to the feedback input port 461b of the servo amplifier 461 to provide accurate speed control of the motor 460 through the servo amplifier 461.
  • This loop is referred to as the first loop or the "Servo Loop" in the figure.
  • the servo amplifier 461 is an off-the-shelf amplifier that provides very accurate control of the speed of the injector motor 460 through this standard Servo Loop configuration and requires little further control.
  • the quadrature encoder signal is also fed back through a signal conditioning Decode Circuit indicated at 472 to a pair of counters 473 and 474 which respectively provide cumulative count signals to the embedded processor 412 and the PC processor 410 respectively.
  • the Analog Current and Analog Speed signals from the output ports 461d and 461e respectively of the servo amplifier 461 are directly fed as input signals to the embedded processor 412 and are respectively applied to first signal inputs of comparators 462a and 462b of the "motor status overspeed overtorque" functional block 462.
  • the reference signal inputs for the comparators 462a and 462b are connected to receive input signals from the PC processor 410 corresponding to "torque reference" and "speed reference” input signals.
  • the comparators 462a and 462b respectively compare the feedback signals received from the servo amplifier 461 with the reference voltage signals received from the PC processor 410 and provide signal outputs representing "overtorque” and “overspeed” respectively to both the embedded processor 412 and the PC processor 410, as indicated in FIG, 12,
  • the master PC processor 410 instructs the embedded processor 412 to perform the injection.
  • the embedded processor is told by the PC processor what the desired flow rate and maximum pressure allowed conditions are.
  • the PC processor sets reference voltage values in the two comparators 462a and 462b, one being representative of the maximum flow rate the embedded processor is allowed to achieve and the other representing the maximum allowable pressure.
  • the "Analog Current” and the “Analog Speed” feedback signals from the servo amplifier 461 are fed back to the comparators 462a and 462b.
  • the embedded processor 412 uses the digital encoder 463 to determine the current position of the ram or syringe piston. Di the preferred embodiment, for each millimeter of contrast material injected 1,317 counts are received from the encoder 463. As the piston moves during an injection, the embedded processor looks at the current position of the ram or piston every ten milliseconds. The embedded processor then calculates the theoretical position of the ram based on a simple trapezoidal type move. If the current position is more than a predetermined number of millimeters different than the actual position, the injection is stopped and error is reported.
  • the potentiometer 464 which provides the "Analog Position" signal is used in a similar fashion, however its tolerance is higher.
  • the system calculates a constant that is representative of the number of ohms per millimeter of movement.
  • the embedded processor uses the same theoretical trapezoidal move to determine the theoretical position of the piston. As with the digital encoder process, if the current position of the ram is more than a predetermined number of ohms different than the actual analog position reading, the injection is stopped and an error is reported.
  • a nested loop control network is established wherein the primary direct Servo feedback loop control of the motor 460 is supplemented by the "Error Loop” control provided through the encoder signal which is fed back through the decoder circuitry 472 and counter 473 and embedded processor 412 back to the signal input terminal 461c of the servo amplifier 461.
  • the first or "servo loop” is a standard velocity control loop that uses proportional integration; whereas the outer “error loop” is a position control loop which simply periodically checks on the servo loop control to ensure that the servo loop is accurately controlling the motor speed.
  • the potentiometer which is operatively connected to the gear train output of the motor 460 is an absolute position sensor that simply acts as a back-up to the encoder loop.
  • the encoder feedback to the PC processor 410 through counter 474 acts as a redundant back-up to the primary error loop control through embedded processor 412, should the processor 412 fail to operate in its intended manner in providing speed correction signals through the secondary "error loop”.
  • the availability of multiple processors provides the capability of true multi-redundancy sensing using intelligence in both sensing circuits.
  • the dual or multiple processor feature provides the capability for redundant control and monitoring safety features of key functions of the system such as injection motor movement and peristaltic motor movement. Both of these conditions are actively monitored by both microprocessors as described above, and as indicated in FIGS. 11 and 12.
  • an "overspeed safety circuit" for the injection motor is provided by the quadrature encoder 463 feeding signals through the decode circuitry 472 and the pair of counters 473 and 474 to the two processors.
  • the use of two independent processors for receiving the encoder information acts as a safety circuit for sensing the flow rate, since both the embedded and PC processors count pulses to determine the injection flow rate. As stated above, the individual counts are accumulated over a specified time interval and the average speed is computed.
  • the safety feature is provided by the fact that either processor may independently shut down the injector motor based on its own decision making capability, in the event of an overspeed condition. Such redundant sensing path dual processor control allows for safety monitoring in the event of a single component failure.
  • an "over volume safety circuit” is provided by the same hardware used to provide the over-speed safety circuit.
  • the pulses provided through counters 473 and 474 from the encoder to the embedded and PC processors allow both processors to independently count pulses to determine injection volume. Either processor may independent shut down the injector motor in the event of an over- volume condition.
  • a further dual safety feature which does not require multiple processors, is provided by the "analog position" signal received from the potentiometer 464 which allows the embedded processor to check the volume by reading the change in the analog voltage output from the potentiometer. By providing the potentiometer as a back-up for the quadrature encoder, further dual redundancy safety is provided for sensing the injection volume.
  • Dual redundant motor safety circuits are provided as previously described for the injector motor "over current” and “overspeed” conditions. These circuits were previously described with respect to comparators 462a and 462b.
  • the comparator 462a uses the “analog current” feedback signal from the servo amplifier 461 to provide dual input signals to both the embedded and PC processors to provide dual processor current measurement safety circuit sensing.
  • comparator 462b applies dual input signals to both of the processors as the result of the "analog speed" signal from the servo amplifier 461 to provide dual redundant sensing of the injector motor speed.
  • the peristaltic pump 44' Similar safety circuits are provided for control of the peristaltic pump 44'. As indicated in FIG. 11 , the peristaltic pump also includes an overspeed/overtorque network 451. In the preferred embodiment, the peristaltic pump 44' is not a brushless motor like the injection motor, and receives a pulse width modulated input signal from the PWM control circuitry 450. Pump motor 44' develops a back EMF that can be sensed and used as a feedback signal along with the output current from the motor driver circuit 450.
  • An electrical block diagram representation of the peristaltic pump safety circuits is illustrated in more detail in FIG. 13. Referring thereto, the PC and embedded processors are indicated at 410 and 412 respectively. The safety circuit illustrated in FIG.
  • a pair of comparators 451a and 451b of the overspeed/overtorque network 451 are used in manner similar to the comparators 462a and 462b previously described with respect to the safety circuits of the injector motor.
  • the comparator 451a provides an overtorque output signal to both of the processors
  • the comparator 451b provides an overspeed input signal to both of the processors.
  • Comparator 451 receives a torque reference voltage signal from the PC processor 410 and the comparator 451b receives a speed reference voltage signal from the processor 410.
  • the comparator 451a monitors a current output signal from motor driver network 450 and provides an output signal whenever the monitored current output signal exceeds the torque reference signal provided from processor 410.
  • the comparator 451b monitors a back EMF signal from motor 44' and provides an output signal whenever the back EMF signal exceeds the speed reference voltage signal applied by processor 410.
  • the embedded processor 412 provides the primary drive control signal to the motor driver 450. In the embodiment of the invention illustrated in FIG. 9, all operator/user interface with the system is performed through the control panel, except for turning on the power supply and activation of the emergency stop switch. Communication with the processor or processors of the system is performed through switches on the touch screen 432 overlying the display 433.
  • the computer generates various screens on the display, with appropriate simulated switch indicators that align with touch pads on the touch screen, which enable the operator to communicate with the microprocessor(s) through the touch screen.
  • the control panel display When power is initialized to the system, the control panel display will communicate to the user that the system is performing self diagnostic tests. Following the diagnostic and calibration tests, the display will illustrate various set-up windows providing a series of instructions for the operator that will guide the operator through the step-by-step set-up procedure, generally including syringe loading, locking and filling, disposable connections, and flushing.
  • FIGS. 14-17 Sample screens that are generated by the PC processor and which are displayed to the user for the power-up, calibration and self diagnostic functions are illustrated in FIGS. 14-17.
  • the initial Power-up screen is illustrated in FIG. 14. This screen remains visible while the system runs in an internal diagnostic check to make sure all functions are working properly. The system will then automatically begin set-up and calibration.
  • the screen of FIG. 15 will appear as the syringe ram moves to a back position, after which the screen of FIG. 16 will be displayed which instructs the operator how to load the syringe assembly.
  • the operator pushes the "Done" pad on the touch screen of FIG. 16.
  • the system is now ready to begin the "set-up” procedure, and displays the screen of FIG. 17 while the syringe ram is moved to its forward position.
  • the "set-up" instructions begin with the screen of FIG. 18.
  • the operator is instructed in a step-by- step manner as to how to load the tubing assembly portion of the system.
  • the operator When the operator has completed the steps identified in FIG. 18, he activates the touch screen by pushing the "Done" switch, and proceeds to the steps indicated on the screen of FIG. 19.
  • the screen of FIG. 19 includes flushing operations of the pressure dome, manifold and fluid lines.
  • the set-up instruction screen of FIG. 20 will be displayed.
  • Screen 20 provides instructions for attaching the pressure transducer and pump assemblies of the system.
  • the operator Upon completion of the set-up instructions, before the system proceeds with filling of the syringe, the operator must activate the "OK" switch of the screen of FIG. 22. Upon activation of the "OK" switch, the system will proceed through an automated filling and purging operation. As the syringe piston is withdrawn to the rear of the syringe, drawing contrast material into the syringe, the screen of FIG. 23 will be displayed. Then, as the piston reverses direction and begins moving forward, air will be purged out of the upper port of the syringe, during which time the screen of FIG. 24 will be displayed. The syringe piston automatically stops before the lower valve within the patient manifold moves.
  • the screen of FIG. 25 will be displayed, providing instructions to the operator as to how to proceed with the purging of the line from the syringes lower port to the system's high pressure line.
  • the operator In order to purge the line, the operator must press and hold the "Purge” switch of the FIG. 25 screen and visually observe the purging process as air and bubbles are pushed out of the line between the syringe and the patient manifold, and from the front/nose of the patient manifold and out into the high pressure line.
  • the operator releases the "Purge” switch and activates the "Done” switch of the FIG. 25 screen.
  • the screen of FIG. 26 When the operator is engaging the "Purge” switch, the screen of FIG. 26 will be displayed.
  • the screen of FIG. 25 When the operator releases contact with the "Purge” switch, the screen of FIG. 25 will reappear. After the "Done" switch of FIG. 25 has been activated, the display screen of FIG. 27 will be displayed.
  • FIG. 27 process steps relate to the final saline flush procedure.
  • the system When the operator engages the "Flush" switch of the FIG. 27 screen, the system will flush the line from the saline bag to the stopcock, assuring that no air bubbles are present in the line. As long as the operator continues to engage the "Flush” switch of the FIG. 27 screen, the screen of FIG. 28 will be displayed.
  • the operator Upon completion of the final saline flush procedure, the operator will release the "Flush” switch and engage the "Done” switch of the screen of FIG. 27, which will cause the display screen of FIG. 29 to be displayed.
  • the FIG. 29 screen is the final start-up screen. Following completion of the instructions of the FIG. 29 screen, the operator activates the "Done" switch of the display, completing the start-up procedure, and the system is now ready for connection to a catheter.
  • the system Upon successful completion of the start-up procedure described above, the system displays the MAIN screen, generally indicated in FIG. 30.
  • the MAIN display screen of the control panel of a preferred configuration thereof is divided into sections as illustrated in FIG. 30. It will be appreciated that all of the formatting for the display screen is provided by and under control of the PC microprocessor 410.
  • the icons for these four function soft keys are aligned with appropriate switch pads of the touch screen 432 so that an operator can press selected ones of the function keys and bring up the status window for the chosen function.
  • the Status window is indicated at 505, and an Indicator window is located at 506.
  • the Status window is used to display system messages and to provide feedback to the user on the state of system operations.
  • the Status indicator window 506 displays key system sensors when they are active.
  • LCA left coronary artery
  • RCA right coronary artery
  • LV/Ao left ventricle/aorta
  • a verbal indication of the selected injection key is indicated at the very top of the display screen. In the sample screen indicated in FIG.
  • the LCA key has been selected and its associated indication "LEFT CORONARY" is displayed at the top of the screen.
  • the following parameters can be changed by pressing the icon of the desired parameter while the Injection Status window is open, or during the set-up procedure: Flow Rate; Injection Volume; Injection Pressure; and "Rise Time”.
  • the injection parameter/limit keys are located along the top of the display screen.
  • a "Flow Rate" window 512 displays the greatest flow rate obtainable if the hand remote controller is completely depressed.
  • the units for flow rate are ml/sec.
  • “Injection Volume” panel 513 displays the total volume limit that can be injected during a single injection. The units for this parameter are ml.
  • An “Injection Pressure” window 512 displays the maximum pressure within the syringe allowed during an injection. If this pressure is reached, a warning light will come on and the injection flow rate will be limited to the indicated pressure. The units for pressure are psi.
  • a “Rise Time” window 515 displays the maximum rise time allowed during an injection. The units for rise time are seconds.
  • the system has the unique ability to either automatically or manually refill the syringe, as described in U.S. Patent No. 5,800,397, entitled Angiographic Injector System with Automatic High/Low Pressure Switching", which is hereby incorporated by reference.
  • the "Refill” key is located in the lowermost portion of the display screen comprises the "Options" portion of the display screen.
  • the Refill key, generally indicated at 517 can be reset at any time during a case or procedure by simply pressing the desired icon.
  • a second Option key generally indicated as the "Rate Type” key is located at 518 which permits selection of the injection procedure as either a "Fixed” rate or a “Variable” rate which can be controlled in real time by the remote hand controller 14'.
  • the processor provides real-time information to the user on the instantaneous conditions existing during an injection procedure. These conditions are displayed in the Status window 505 as indicated on the sample screen of FIG. 31.
  • the display panel also displays the results of the last injection in a "Last Injection” window 520.
  • the last injection results include the “total volume” and the "maximum flow rate" of the last injection performed.
  • the display panel also indicates the cumulative total of contrast material that has been injected in a patient for the current case, indicated in the "Contrast Total" display window 522.
  • the Last Injection and Contrast Total display windows are located near the lower left portion of the display screen.
  • the Contrast Total display provides important information to have instantaneously available during the injection procedure, since a case procedure may involve numerous filling procedures of the syringe. Further, such filling procedures may represent either total or only partial filling of the syringe. Prior techniques depended upon the operator/user for maintaining a log of the total amount of contrast material that had been administered to a patient over the course of successive injections. Failure to maintain an accurate cumulative total for the amount of contrast material injected can result in overdose of injected material to the patient.
  • a display window/key indicated as a "Patient's Weight” is indicated at 524.
  • this display window displays the weight of the current patient. Selection of this key will allow the user to enter a patient's weight in kilograms into the system. The patient weight is used to calculate injection values and limits (hereinafter described in more detail).
  • the final key on the display panel is the "End Case" key 526 located near the lower right portion of the display panel. Activation of this key will prompt the user through the proper steps before shut-down of the system or before starting a new case.
  • the Emergency button or switch 434 (FIG. 11) is physically located on the upper right hand portion of the control panel. This is the only functional switch (besides the Power Supply switches) which is not located on the display screen. The Emergency switch disables any on-going function and displays a message in the status window that the emergency button is engaged.
  • the emergency button or switch is an alternate action type of switch. When engaged, the button is lit. To disengage the switch the user must press the button again.
  • the injection limits can be changed by pressing the key (512-515) of the desired parameter. If the injection (key 518) is set to a "Fixed" mode, a keypad will be presented to the user in the status window. This condition is illustrated in FIG. 32. A new value can now be entered. This new value will be checked by the processor to see if it within an acceptable range for the type of ejections elected. If the entered value is out of the acceptable range, a message will be displayed indicating this fact to the user. If the "Cancel" key is pressed, the previously set value will remain set. If the injection option (key 518) is set to the "variable” mode, a choice of six different values are displayed in the status window for the user to select. A sample display window corresponding to this situation is illustrated in FIG. 33. If the "Cancel" key is pressed, the previously set value will remain set.
  • An Injection is initiated by pressing the "Inject" button or key 500. If the LV/Ao (large injection button), is selected, the user will be asked to confirm this.
  • the LV/Ao injection procedure represents the largest volume use of contrast material; whereas the RCA injection procedure uses the least amount of contrast material.
  • the user is then asked by prompt on the display if it is okay to "Arm" the injection. The user must press the "OK” key in the status window.
  • the system will prompt for a refill.
  • the refill will be automatic or manual, depending on the status of the "Refill” option key 517.
  • the volume level is correct, the user will be prompted to activate the hand controller 14' for initiating the injection procedure.
  • volume injected is less than 10% of the volume limit, the number of injections will not increase and the hand controller will remain armed.
  • a "large” injection requires the user to press “Large OK” again before another injection is permitted. The user exit the inject function by pressing any key on the screen.
  • the Saline Flush function initiated by activation of the "Saline” key 501, pulls saline from the saline bag and flushes the disposable and line connections.
  • the "Saline Flush” status window will be displayed with a “Flush” key and a “Done” key. Pressing the “Flush” key will flush the disposable with saline for up to 10 seconds or until the user stops pressing the key. Pressing the "Done” button in the window will end the flush process and return the user to the "MAIN" screen.
  • the Aspirate function draws line fluid back into the waste bag from the catheter through the disposable. It may be used to remove bubbles if they are detected in the line.
  • the aspirate function is initiated by selecting the "Aspirate” button or key 502 on the display panel.
  • the "Aspirate” status window will be displayed on the screen. Pressing the “Aspirate” key will pull line fluid back through the disposable into the waste bag as long as the "Aspirate” key is depressed, for up to 10 seconds. Pressing the "Done” button will return the user to the "MAIN" screen.
  • the manual purge function is used to flush air from the disposable.
  • Syringe Purge involves purging air out-of the syringe and will be stopped when air has been purged from the syringe and the fluid pushes the syringe check valve closed.
  • Line Purge purges air from the syringe to the stopcock through the patient manifold. This method will send contrast material through the disposable and will disengage the bubble detection device. This purge is done at system start-up in order to clear air out of the interconnect of the syringe to the patient manifold and the front on the patient manifold valve.
  • Line Purge may also be used when an air bubble remains within the disposal after the aspirator flush procedures have been tried.
  • the "Purge” key 503 is selected from the "MAIN" screen.
  • the "Purge” status window will be displayed. Three options are presented on the screen: “Syringe”, “Cancel”, and “Line”. Selecting "Cancel” will return to the "MAIN" screen. If “Line” is selected, the user is warned to disconnect the patient. The user must acknowledge this by pressing the "okay” key. At this point, or if "Syringe” has been selected, a "Purge” key and "Done” key are displayed in the window.
  • the "Purge” key is a press and hold key which will initiate and continue the purging through the line or syringe until the user releases the key, for up to 10 seconds.
  • the purge will stop automatically if the air is completely purged out and the contrast valve is successfully closed. If the user stops the purge before the valve closes, a message will indicate that the purge is not complete. Pressing the "Done" key or any other key on the screen will exit the purge function.
  • a sample screen for a manual purge function is illustrated in FIG. 34.
  • the syringe will automatically refill to 110 ml. if there is not enough contrast media within the syringe for the desired injection volume limits. This will occur automatically at the time of injection.
  • the "Refill” status window will be displayed.
  • a "Purge” key, a “Done” key, and a “Refill” key are active in this window. Pressing and holding down the “Refill” key will draw the plunger back, filling the syringe. The current amount of contrast media in the syringe is displayed as it fills. When the "Refill” button is released, the refilling operation discontinues.
  • prior systems have included memory recall features for stored injection parameter values that may have been stored by a physician for a particular patient or for a particular procedure wherein the stored parameters represent the typical injection parameter choices of that physician.
  • Various embodiments of the present invention provides an automated method for determining suggested default injection parameter values just prior to an injection procedure, which injection parameter values are directly related to values or conditions of the patient to be treated.
  • the injection parameter default values are calculated using the "weight" of the patient. As stated above, however, other unique patient factors could be used in creating the default value calculations.
  • Table 1 provides a listing of calculated default injection parameter values determined by Equations 1-4 for selected patient weights.
  • Table 2 provides a listing of values of the four injection parameter values determined by Equations 5-8 for selected patient weights.
  • LV/Ao injection selection (Left Ventricle/ Aorta procedure), for the preferred embodiment, are calculated according to Equations 9-12.
  • Table 3 illustrates default injection parameter values determined by 9-12 for selected patient weights.
  • FIG. 36 illustrates comparative graphs for the default injection parameter values for Flow Rate Limits determined according to Equations 1, 5 and 9 respectively for the Left Coronary, the Right Coronary and the Left Ventricle/ Aorta functions for patient weights from 10-130 kg.
  • FIG. 37 illustrates comparative graphs of the Volume Limit default injection parameter calculated according to Equations 2, 6 and 10 for the Left Coronary, the Right Coronary and the Left Ventricle/ Aorta selections respectively for patient weights ranging from 10-130 kg.
  • the automated determination of default injection parameter values based on the patient's unique characteristics (such as weight), minimizes guess factors associated with selection of proper default parameters for a particular patient, provides a method of determining the default parameters which accommodates changes in the patient's condition between injection procedures and eliminates the requirement for supplemental charts and graphs upon which the physician or operator administering the injection procedure might have to otherwise rely in order to select or determine proper injection parameter default values.
  • the user need simply select one of the three injection selectors provided by selection buttons 508-510 and to enter the patient's weight in kilograms in the patient weight window 524.
  • a flow chart of this process is illustrated in FIG. 38.
  • the operator enters the patient's weight (block 531).
  • the microprocessor automatically determines the default injection parameters by using the appropriate algorithms therefor (block 532) according to the selected injection procedure (i.e., LCA, RCA or LV/ Ao) and according to the patient weight entered into the system through the display panel.
  • FIG. 39 is a block diagram of one embodiment of a powered injection system 600. This powered injection system 600 may also be configured and used to perform the method shown in FIG. 41 (described in more detail below).
  • the system 600 includes a control panel/user interface for controlling and interfacing with the system 600, and an injector head that includes a motor/actuator assembly for driving a drive mechanism in a syringe 616.
  • the control panel 602 allows a user to select and/or program various parameters of the injection system, such as is described previously with regards to control-panel functionality.
  • Connector 604 couples a hand-control device 612 to the control panel 602.
  • the hand- control device 612 allows a user to manually control an injection procedure, and may comprise a pneumatic, electronic, or other form of hand-control device.
  • the injection system 600 is capable of injecting fluid from a reservoir 614, such as a bottle of contrast media, and/or fluid from a reservoir 606, such as a bag of diluent.
  • a reservoir 614 such as a bottle of contrast media
  • a reservoir 606 such as a bag of diluent.
  • the system 600 is capable of injecting a mixture of fluids from the reservoirs 614 and 606 through coordinated operation of the syringe 616 and pump 610.
  • the pump 610 is capable of pumping fluid from the reservoir 606.
  • the pump 610 comprises a peristaltic pump.
  • Tubing from the reservoir 606 runs through the pump 610 in tubing 608.
  • Tubing 608 runs through a transducer 618 and into valve 620.
  • the transducer 618 is used for measuring hemodynamic pressure signals from a patient and generating representative signals that can be propagated to an external monitoring device, according to one embodiment.
  • the valve 620 controls the flow of fluid to output tubing 622, according to one embodiment.
  • the valve 620 allows only fluid from the reservoir 614 or from the reservoir 606 to be selectively injected at one time.
  • the valve 620 may allow a mixture of fluids to be injected.
  • the valve 620 is part of the manifold described earlier (in previously described embodiments).
  • the syringe 616 may be a dual-port syringe. One port is coupled to the reservoir 614, and one port is coupled to the valve 620. In an alternate embodiment, a single-port syringe may be used.
  • Output tubing 622 runs through air detector 624, which is used to detect air (e.g., air bubbles, air columns) in the tubing 622.
  • air detector 624 An acoustic, optical, or other form of air detector may be used.
  • a signal is sent to the control panel 602 to alert the user via the user interface.
  • the system 600 is capable of pausing, terminating, or aborting an injection procedure if the air detector 624 has detected air in the line 622.
  • the output tubing 622 is also coupled to a stopcock 626.
  • a user may manually operate the stopcock 626 to couple or decouple the tubing 622 with a patient line. If the stopcock is also coupled to a separate device, such as a hand syringe, the user may manipulate the stopcock 626 to couple the patient line with this separate device, rather than the tubing 622.
  • FIG. 40 is a block diagram of an alternate embodiment of a powered inj ection system 700.
  • This powered injection system 700 may also be configured and used to perform the method shown in FIG. 41.
  • the system 700 of FIG. 40 is a dual-syringe system that includes a control panel 702 and two motor/actuator assemblies 702a and 702b. Each motor drives one of the linear actuators in the assemblies 702a, 702b.
  • Each linear actuator drives a drive mechanism, such as a plunger, into and out of one syringe (708a or 708b).
  • the drive mechanism can thereby engage a wiper (such as a plastic or silicone wiper) in the syringe 708a or 708b, where the wiper comes into contact with the fluid within the syringe.
  • An individual drive mechanism of the system 700 can move within the syringe barrel of each syringe 708a and 708b in either a forward or rearward direction.
  • the forward direction is a direction towards the input/output port(s) of the syringe, while the rearward direction is an opposite direction.
  • the drive mechanism injects liquid or purges air out of the syringe 708a or 708b.
  • the drive mechanism fills liquid into the syringe 708a or 708b.
  • one syringe is used for contrast, and the second syringe is used for saline.
  • each syringe 708a and 708b is capable of drawing in fluid from a reservoir 706 (such as, for example, a bag of diluent), and the syringe 708b is capable of drawing in fluid from a reservoir 704 (such as, for example, a bottle of contrast media).
  • each syringe 708a and 708b is a dual-port syringe, having one input port and one output port (as is shown in the example of FIG. 40).
  • each syringe 708a and 708b is a single-port syringe. Two sets of pinch valve/air detect assemblies are shown in the system of FIG. 40.
  • Tubing from one fluid reservoir runs through an individual pinch valve/air detect assembly 710a or 710b and then into a syringe input port.
  • tubing from the reservoir 706 runs through the assembly 710a and then into the input port of the syringe 708a
  • the tubing from the reservoir 704 runs through the assembly 710b and then into the input port of the syringe 708b.
  • Tubing leading from the output ports of the syringes 708a and 708b run through additional pinch valve/air detect assemblies 712a and 712b.
  • tubing leading from the output port of the syringe 708a runs through the assembly 712a
  • tubing leading from the output port of the syringe 708b runs through the assembly 712b.
  • the tubing running through the assemblies 712a and 712b meet in a Y-connector 714, which may further comprise a valve.
  • the Y-connector 714 leads to patient line tubing which may be coupled to a patient catheter for injection of fluid into a patient.
  • Each pinch valve in the assemblies 710a, 710b, 712a, 712b may be opened or closed by the system 700 to control the fluid connections leading to or away from the syringes 708a and 708b.
  • the pinch valves may selectively open or close to block or unblock the fluid pathways through the respective tubing.
  • the air detect sensors in the assemblies 710a, 710b, 712a, 712b may be optical, acoustic, or other form of sensors. These sensors help detect air (e.g., air bubbles, air columns, etc.) that may be present in the fluid pathways leading to or away from the syringes 708a, 708b. When one or more of these sensors generates a signal indicating that air may be present in a fluid line, the system 700 may warn the user or terminate an injection procedure. Having multiple such air detect sensors on the input and output sides of the syringes 708a and 708b helps improve the safety in use of the system 700.
  • the system 700 is capable of injecting a mixture of fluids from the reservoirs 704 and 706 through coordinated injection of fluids from the syringes 708a and 708b.
  • valve types other than pinch valves may be used within the system 700.
  • the system 700 of FIG. 40 is also capable of implementing the method shown in FIG. 41. Performing this method will help remove air bubbles from the tubing leading from one or both of the syringes 708a, 708b shown in FIG. 40.
  • FIG. 41 is a flow diagram of a method for purging air bubbles, according to one embodiment. This method may be performed by an automated or powered fluid injection system, such as the system shown in FIG. 1, the system shown in FIG. 39, or the system shown in FIG. 40. In the dual-syringe system that is shown in FIG. 40, the method may be performed for either or both of the syringe/actuator assemblies.
  • an automated or powered fluid injection system such as the system shown in FIG. 1, the system shown in FIG. 39, or the system shown in FIG. 40.
  • the method may be performed for either or both of the syringe/actuator assemblies.
  • a first act in the method is to drive the drive mechanism (e.g., plunger) within the syringe to a forward, or extended, position.
  • the drive mechanism may engage the wiper within the syringe during this operation.
  • the motor/actuator is used to drive the drive mechanism in a forward direction to such an extended position.
  • Air or liquid (fluid) may be purged from within the syringe (such as syringe 18 shown in FIG. 1, the syringe 616 shown in FIG. 39, or one of the syringes 708a/708b shown in FIG. 40) after the drive mechanism has been moved to this position, or while the drive mechanism is being moved to this position.
  • the drive mechanism is moved to a fully extended position.
  • the motor/actuator causes the drive mechanism to be retracted within the syringe in a rearward direction for a fixed amount.
  • a small, fixed volume of fluid such as contrast or diluent
  • the plunger 20 may be moved in a rearward (or backward) direction within the syringe 18 to draw a small amount of contrast (such as 8 ml) from the bottle 22 into the syringe 18.
  • the system can be configured to move the plunger in a specified or predetermined amount during this act.
  • the system pauses for a short period of time (e.g., 1 second) to allow the fluid to flow into the syringe body.
  • a fluid with a viscosity such as contrast media may take a period of time to flow into the syringe.
  • the system or user may specify or determine the amount of pause time, which may depend on the type or viscosity of fluid being drawn into the syringe.
  • the system causes the drive mechanism to purge possible air back into a fluid reservoir.
  • the motor/actuator 702b may cause the corresponding drive mechanism in FIG. 40 to move in a forward direction a fixed amount to purge possible air from the syringe 708b into the bottle 704.
  • the motor/actuator can cause the drive mechanism to purge air back into the bottle 614 through a one-way valve (not shown).
  • the system then pauses for a short period of time to allow the air to flow through into the fluid reservoir.
  • a one-way valve between the syringe and the fluid reservoir allows air to flow from the syringe into the reservoir, but does not allow fluid to flow from the syringe back into the reservoir.
  • the volume of fluid purged during this act e.g., 5ml
  • the volume of fluid purged during this act is smaller than the volume of fluid initially filled into the syringe during the prior act (e.g., 8ml). In this embodiment, a small amount of fluid remains within the syringe after this initial air purge.
  • a user such as a physician visually inspects the syringe and syringe chamber and determines whether any large air bubbles are present or visible. The user then interacts with the user interface of the syringe to provide user input regarding the existence or non-existence of such bubbles.
  • the system is capable of automatically detecting the presence or large air bubbles within the syringe. Optical, acoustic, or other means may be used to detect the presence of larger size bubbles in the forward section of the syringe (near the port openings).
  • the system will repeat a series of the acts described above (and as shown in the flow diagram of FIG. 41) through one or more iterations until such larger- size bubbles have been removed.
  • the system determines the number of iterations that will be executed. For example, the system may make this determination based on one or more properties of the liquid (such as viscosity) or the amount of extension of the drive mechanism during the initial act of the purge operation.
  • a user may manually input one or more properties of the liquid using a control panel, or the system may determine these properties automatically (such as by the use of bar-code readers, RFID or radio-frequency identification signals, etc.)
  • the system removes smaller-size air bubbles that may still be present in the syringe and that may be clinging to the syringe walls.
  • the system closes valves that are coupled to the input and output ports of the syringe (such as ports 78 and 80 shown in FIG. 1). For example, in FIG.
  • the system may close valves in the assemblies 710a and 712a for an operation of the syringe 708a, or may close the valves in the assemblies 710b and 712b for an operation of the syringe 708b.
  • These valves may comprise pinch valves, according to one embodiment. Although these valves are not explicitly shown in FIG. 1 , they may be coupled to ports 78 and 80 and may be used to close (and later open) the fluid connections coupled to ports 78 and 80. In one embodiment of the system shown in FIG. 39, valves coupled to the input and output ports of the syringe 616 may be implemented to close during this act, as well.
  • the system retracts the drive mechanism (in the rearward direction) within the syringe a fixed amount to vacuum expand any remaining small bubbles.
  • the system then pauses a short period of time to allow the vacuum- expanded bubbles to coalesce and migrate to the top front (or forward portion) of the syringe.
  • the system drives the drive mechanism in the forward direction a fixed amount, which may be the same amount as the drive mechanism was moved in the rearward direction to vacuum-expand the bubbles (previously described).
  • the system then opens the valve leading to the fluid container (such as bottle 22 in FIG. 1, the bottle 614 in FIG. 39, or the reservoirs 704 or 706 in FIG. 40) and purges remaining small air bubbles into the container.
  • the system is capable of retracting the drive mechanism in the rearward direction to fill (either partially or completely) the syringe with fluid, such as contrast media.
  • fluid such as contrast media.
  • air has been removed from the syringe, and the system is now ready to inject fluid from the syringe into the patient.
  • air bubbles are purged, or removed, from the syringe prior to a substantial fill operation.
  • the injection system may be available for use during an emergency situation in a shorter period of time.
  • the syringe would be completely purged and ready to inject before a full fill procedure is completed.
  • the user may be able to interrupt the fill and inject fluid into the patient, since air bubbles have already been removed from the fluid chamber.
  • air pressure inside the fluid bottle may possible be minimized, which can help reduce the problems with wet air vents and/or popped bottle spikes that couple the container with the tubing leading to the syringe.
  • An early purge reduces unsightly air bubbles at the top of the syringe. These bubbles arise during the filling process and may agitate the contrast/air bubble causing small bubbles to break away from the original bubble. By purging air at the front of the syringe initially, this problem can be reduced. Also, allowing a fill operation to occur after the air purge may potentially force the vent to be used which may remove contrast from the filter in the spike mechanism and clear the vent port. Thus, minimal contrast may be left to clog the filter.
  • the staggered nature of the initial air purge has another potential benefit of combining the filling procedure with the air purge, which may shorten the total time of the sequence. Another potential benefit is that there would not need to be an unequal exchange of volume from syringe to bottle. The larger retraction with a small delay allows the same (or greater) volume of fluid to be extracted from the bottle as the volume of possible air that is purged back into the bottle. This may result in no net pressure increase in the bottle.
  • the system causes the motor/actuator to move the drive mechanism in varying amounts in different acts, according to one embodiment.
  • the system also pauses for certain periods of time during certain acts.
  • These parameters may configurable within the system or by a user, depending on the nature of the injection, type/viscosity of fluid, etc.
  • the system includes default parameters that may be configurable within certain, predefined limits.

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Abstract

Un mode de réalisation de l'invention concerne un procédé de purge de l'air d'une unité de pressurisation utilisée dans un système d'injection de fluide. Dans ce mode de réalisation, le procédé comporte les étapes consistant à: déplacer un mécanisme d'entraînement vers l'avant, dans une position déployée, dans une unité de pressurisation; retirer le mécanisme d'entraînement vers l'arrière afin de remplir partiellement l'unité de pressurisation d'une première quantité de fluide médical; déplacer le mécanisme d'entraînement vers l'avant afin d'éliminer l'air de l'unité de pressurisation; et retirer le mécanisme d'entraînement vers l'arrière afin de remplir l'unité de pressurisation d'une seconde quantité de fluide, cette dernière étant supérieure à la première quantité de fluide.
PCT/US2007/067982 2006-05-11 2007-05-02 Purge d'air dans un système d'injection de fluide WO2007133942A2 (fr)

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Cited By (27)

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JP2015217176A (ja) * 2014-05-19 2015-12-07 株式会社根本杏林堂 薬液注入装置
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JP5985188B2 (ja) * 2010-02-12 2016-09-06 株式会社根本杏林堂 薬液注入装置および薬液注入システム
US9446193B2 (en) 2011-04-12 2016-09-20 Roche Diagnostics International Ag Dosing unit for an infusion pump device
WO2018089882A1 (fr) 2016-11-14 2018-05-17 Bayer Healthcare Llc Procédés et systèmes de vérification du contenu d'une seringue utilisée pour l'administration de fluide médical
DE102017111301A1 (de) 2017-05-23 2018-11-29 B. Braun Melsungen Ag Sensorsystem
CN109350114A (zh) * 2018-11-28 2019-02-19 广东省人民医院(广东省医学科学院) 一种多功能心脏彩超声学造影检查装置
WO2019204617A1 (fr) * 2018-04-19 2019-10-24 Bayer Healthcare Llc Procédé d'élimination de gaz d'un réservoir
US10898638B2 (en) 2016-03-03 2021-01-26 Bayer Healthcare Llc System and method for improved fluid delivery in multi-fluid injector systems
US11141535B2 (en) 2017-08-31 2021-10-12 Bayer Healthcare Llc Fluid path impedance assessment for improving fluid delivery performance
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US11478581B2 (en) 2017-08-31 2022-10-25 Bayer Healthcare Llc Fluid injector system volume compensation system and method
WO2022265695A1 (fr) * 2021-06-17 2022-12-22 Bayer Healthcare Llc Système et procédé de détection de type de fluide dans un tube pour appareil d'injection de fluide
US11598664B2 (en) 2017-08-31 2023-03-07 Bayer Healthcare Llc Injector pressure calibration system and method
US11779702B2 (en) 2017-08-31 2023-10-10 Bayer Healthcare Llc Method for dynamic pressure control in a fluid injector system
US11786652B2 (en) 2017-08-31 2023-10-17 Bayer Healthcare Llc System and method for drive member position and fluid injector system mechanical calibration
US11839751B2 (en) 2020-06-18 2023-12-12 Bayer Healthcare Llc In-line air bubble suspension apparatus for angiography injector fluid paths
US11938093B2 (en) 2020-02-21 2024-03-26 Bayer Healthcare Llc Fluid path connectors for medical fluid delivery
US12023464B2 (en) 2020-12-01 2024-07-02 Bayer Healthcare Llc Cassette for retention of fluid path components for fluid injector system
US12048835B2 (en) 2020-08-11 2024-07-30 Bayer Healthcare Llc Features for angiography syringe
EP4201442A4 (fr) * 2020-09-11 2024-08-21 Se Hoon Chin Système d'actionnement de seringue
US12070568B2 (en) 2020-02-28 2024-08-27 Bayer Healthcare Llc Fluid mixing device and fluid delivery tube set including same
US12208239B2 (en) 2018-08-28 2025-01-28 Bayer Healthcare Llc Fluid injector system, method of preventing fluid backflow, and computer program product
US12251544B2 (en) 2018-04-19 2025-03-18 Bayer Healthcare Llc System and method for air detection in fluid injector

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US7621892B2 (en) 2003-12-31 2009-11-24 Mallinckrodt Inc. Contrast container holder and method to fill syringes
JP5985188B2 (ja) * 2010-02-12 2016-09-06 株式会社根本杏林堂 薬液注入装置および薬液注入システム
US10525211B2 (en) 2011-04-12 2020-01-07 Roche Diabetes Care, Inc. Infusion pump and method for improved filling of a fluidic system
EP2510961A1 (fr) * 2011-04-12 2012-10-17 F. Hoffmann-La Roche AG Pompe à perfusion avec remplissage amélioré du système fluidique et procédé de remplissage dudit dispositif de pompe à perfusion
US9402951B2 (en) 2011-04-12 2016-08-02 Roche Diagnostics International Ag Infusion pump device and method for improved dosing
WO2012140056A1 (fr) * 2011-04-12 2012-10-18 F. Hoffmann-La Roche Ag Dispositif de pompe à perfusion avec amorçage amélioré du système fluidique et procédé d'amorçage du dispositif de pompe à perfusion
US9446193B2 (en) 2011-04-12 2016-09-20 Roche Diagnostics International Ag Dosing unit for an infusion pump device
US11278853B2 (en) 2013-03-13 2022-03-22 Bayer Healthcare Llc Method for controlling fluid accuracy and backflow compensation
JP2015217176A (ja) * 2014-05-19 2015-12-07 株式会社根本杏林堂 薬液注入装置
US11672902B2 (en) 2016-03-03 2023-06-13 Bayer Healthcare Llc System and method for improved fluid delivery in multi-fluid injector systems
US10898638B2 (en) 2016-03-03 2021-01-26 Bayer Healthcare Llc System and method for improved fluid delivery in multi-fluid injector systems
WO2018089882A1 (fr) 2016-11-14 2018-05-17 Bayer Healthcare Llc Procédés et systèmes de vérification du contenu d'une seringue utilisée pour l'administration de fluide médical
US12263326B2 (en) 2016-11-14 2025-04-01 Bayer Healthcare Llc Methods and systems for verifying the contents of a syringe used for medical fluid delivery
EP3538182A1 (fr) * 2016-11-14 2019-09-18 Bayer Healthcare LLC Procédés et systèmes de vérification du contenu d'une seringue utilisée pour l'administration de fluide médical
JP2023029972A (ja) * 2016-11-14 2023-03-07 バイエル・ヘルスケア・エルエルシー 医用流体送出に使用されるシリンジの内容物を確認するための方法およびシステム
DE102017111301A1 (de) 2017-05-23 2018-11-29 B. Braun Melsungen Ag Sensorsystem
US11701465B2 (en) 2017-05-23 2023-07-18 B. Braun Melsungen Ag Sensor system
US11598664B2 (en) 2017-08-31 2023-03-07 Bayer Healthcare Llc Injector pressure calibration system and method
US11826553B2 (en) 2017-08-31 2023-11-28 Bayer Healthcare Llc Fluid path impedance assessment for improving fluid delivery performance
US12214155B2 (en) 2017-08-31 2025-02-04 Bayer Healthcare Llc Fluid injector system volume compensation system and method
US11478581B2 (en) 2017-08-31 2022-10-25 Bayer Healthcare Llc Fluid injector system volume compensation system and method
US11141535B2 (en) 2017-08-31 2021-10-12 Bayer Healthcare Llc Fluid path impedance assessment for improving fluid delivery performance
US11786652B2 (en) 2017-08-31 2023-10-17 Bayer Healthcare Llc System and method for drive member position and fluid injector system mechanical calibration
US11779702B2 (en) 2017-08-31 2023-10-10 Bayer Healthcare Llc Method for dynamic pressure control in a fluid injector system
WO2019204617A1 (fr) * 2018-04-19 2019-10-24 Bayer Healthcare Llc Procédé d'élimination de gaz d'un réservoir
CN112261959A (zh) * 2018-04-19 2021-01-22 拜耳医药保健有限公司 从储器移除气体的方法
US12251544B2 (en) 2018-04-19 2025-03-18 Bayer Healthcare Llc System and method for air detection in fluid injector
US12208239B2 (en) 2018-08-28 2025-01-28 Bayer Healthcare Llc Fluid injector system, method of preventing fluid backflow, and computer program product
CN109350114B (zh) * 2018-11-28 2023-07-04 广东省人民医院(广东省医学科学院) 一种多功能心脏彩超声学造影检查装置
CN109350114A (zh) * 2018-11-28 2019-02-19 广东省人民医院(广东省医学科学院) 一种多功能心脏彩超声学造影检查装置
US11938093B2 (en) 2020-02-21 2024-03-26 Bayer Healthcare Llc Fluid path connectors for medical fluid delivery
US12070568B2 (en) 2020-02-28 2024-08-27 Bayer Healthcare Llc Fluid mixing device and fluid delivery tube set including same
US11839751B2 (en) 2020-06-18 2023-12-12 Bayer Healthcare Llc In-line air bubble suspension apparatus for angiography injector fluid paths
US12048835B2 (en) 2020-08-11 2024-07-30 Bayer Healthcare Llc Features for angiography syringe
EP4201442A4 (fr) * 2020-09-11 2024-08-21 Se Hoon Chin Système d'actionnement de seringue
US12023464B2 (en) 2020-12-01 2024-07-02 Bayer Healthcare Llc Cassette for retention of fluid path components for fluid injector system
WO2022182935A1 (fr) * 2021-02-26 2022-09-01 Bayer Healthcare Llc Système de détection et de mesure d'air pour injecteur de fluide
US20240207509A1 (en) * 2021-06-17 2024-06-27 Bayer Healthcare Llc System and method for detecting fluid type in tubing for fluid injector apparatus
US12239818B2 (en) * 2021-06-17 2025-03-04 Bayer Healthcare Llc System and method for detecting fluid type in tubing for fluid injector apparatus
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