US20110237932A1 - Method of Operation for a Magnetic Resonance Imaging Suite - Google Patents
Method of Operation for a Magnetic Resonance Imaging Suite Download PDFInfo
- Publication number
- US20110237932A1 US20110237932A1 US13/155,177 US201113155177A US2011237932A1 US 20110237932 A1 US20110237932 A1 US 20110237932A1 US 201113155177 A US201113155177 A US 201113155177A US 2011237932 A1 US2011237932 A1 US 2011237932A1
- Authority
- US
- United States
- Prior art keywords
- power
- injector system
- battery compartment
- power supply
- mri
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
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
- A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
- A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
- A61M5/14546—Front-loading type injectors
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
-
- 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
Definitions
- the invention relates to contrast media power injectors compatible for use within a magnetic resonance imaging (MRI) suite, and in particular, to electrical interconnection of components of a magnetic resonance (MR) injector.
- MRI magnetic resonance imaging
- MR magnetic resonance
- a Magnetic Resonance Imaging (MRI) unit consists of a large cylindrical superconducting magnet for generating a strong magnetic field, devices for transmitting and receiving radio waves, and a complex computer system.
- the strong magnetic field causes the hydrogen nuclei in the patient to line up.
- a low-frequency radio wave is pulsed through the magnet into the patient.
- the hydrogen atoms absorb the energy released by the radio waves. This disrupts the uniformity of the nuclei.
- the radio-wave stimulation stops the nuclei return to their original state and emit energy in the form of weak radio frequency (RF) signals.
- RF radio frequency
- a computer translates the RF signals into highly detailed cross-sectional images.
- the images are essentially maps of the locations of water or hydrogen in the body.
- the magnetic field produced by the MRI unit constrains installation of associated MRI equipment.
- any ferromagnetic object near the MRI unit will be attracted by the magnetic field, either impairing operation of the equipment or becoming a safety hazard if forcibly projected toward the MRI unit.
- the uniformity of the magnetic field of the MRI unit is altered by ferromagnetic material, even if the ferromagnetic material is secured to prevent safety hazards. Consequently, ferromagnetic material is generally kept away from the MRI unit.
- the radio frequency transmissions emitted by the MRI unit toward the patient also poses electromagnetic interference/compatibility (EMIC) constraints on the installation of other equipment.
- EMIC electromagnetic interference/compatibility
- General consumer and medical equipment such as personal computers and monitors are typically inadequately shielded to prevent impairment of function due to the strength of such RF emissions.
- the MRI unit is susceptible to degraded performance if RF noise from other equipment distorts the received RF signal during imaging.
- the core of the MRI unit including the magnetic field producing and RF transmission and receiving portions, is placed within a magnet room that is shielded from the other rooms of the MRI suite and the rest of the facility.
- nonferrous metal sheets or mesh encompass the entire magnet room to prevent magnetic energy and RF energy from entering or leaving the magnet room. Consequently, the MRI unit generally includes highly shielded electrical power, data and control cabling that are routed through filtered and grounded access points so that susceptible or interfering components of the MRI unit may be placed outside of the shielded room.
- contrast media As MRI units became capable of increased computational speed, opportunities were presented for use of contrast media, injected into patients before or during an MRI scan, to enhance dynamic imaging studies.
- contrast media were developed that allowed MRI scanning of certain types of tissues that otherwise were insufficiently distinguishable from surrounding tissue for effective MRI diagnostic studies.
- Power injectors for contrast media are sometimes preferred due to repeatability of dosage volumes and injection rates and keeping personnel away from the MRI unit during a scan.
- adapting contrast media injectors from other radiological modalities e.g., X-ray, Computer-aided Tomography (CT), etc.
- CT Computer-aided Tomography
- a power injector system 10 for injecting image-enhancing contrast media into a patient before or during an MRI scan is depicted as installed in an MRI suite 12 .
- the power injector system 10 depicted is an OPTISTARTM magnetic resonance (MR) digital injection system available from Mallinckrodt, Liebel-Flarsheim Business, Cincinnati, Ohio.
- the system 10 successfully operates within an MRI suite 12 by placement of components at varying distances from an MRI unit 14 or with varying degrees of shielding.
- a power head 16 contains ultrasonic motors. The ultrasonic motors operate syringes to dispense contrast media and saline solution into a patient as commanded and powered over a shielded power head cable 18 by a power control 20 .
- the power control 20 is also within a shielded magnet room 22 of the MRI suite 12 along with the power head 16 and the MRI unit 14 , although generally spaced away from the MRI unit 14 to reduce the EMIC considerations. Since AC outlets are generally not available in the shielded magnet room 22 , the power control 20 is battery powered. The power control 20 provides power to the power head 16 in response to data signals that are relayed from the power head 16 to the power control 20 and between the power control 20 and a touch-screen console 24 outside of the shielded magnet room 22 . In particular, a shielded electrical cable 26 for transferring data signals couples the power control 20 to an opening, such as a free hanging D-shell connector 28 , in a penetration panel 30 .
- An electrical cable 32 outside of the shielded magnet room 22 is electrically coupled to the other electrical cable 26 inside the shielded magnet room 22 via a filter 34 connected to the penetration panel 30 .
- the filter 34 reduces RF noise induced on the cables 26 , 32 .
- the cable 32 passes from an equipment room 36 that is positioned adjacent to the penetration panel 30 to a control room 38 where the MRI unit controls (not shown) and the power injector touch-screen console 24 reside.
- a battery charger 40 is placed in the control room 38 for recharging a battery 42 for use in the power control 20 .
- the battery charger 40 receives its power from an AC outlet 44 .
- an inconvenient task is placed on operators of the MRI unit 14 and battery-powered injector system 10 to monitor the state of charge of batteries 42 and swap batteries between the battery charger 40 and the power control 20 . If an undercharge of batteries 42 installed in the power control 20 is not detected in a timely fashion, the operation of the MRI unit 14 is delayed, reducing the number of patients that may be scanned. Such reduction in the number of patients increases medical costs and limits delivery of medical services.
- the power control 20 provides power for the electronic components and the ultrasonic motors of the power head 16 and the electronic components of the power control 20 itself.
- the power control 20 does not power components outside the magnet room 22 . Consequently, several of the major components of the battery-powered injector system 10 each individually have internal power supplies that regulate and convert electrical power for use by that major component.
- the console includes a power supply that also receives power from the AC outlet 44 and converts the AC electrical power to DC voltages useful for the electronics and display devices therein.
- the battery charger 40 includes an internal power supply that regulates and converts AC power to voltages suitable for its electronics and for the battery 42 being recharged.
- the power control 20 includes an internal power supply for regulating and converting the battery power from installed batteries 42 for the voltages required for its operation. Each internal power supply increases the cost, the size, and the cooling requirement of each major component.
- the present invention addresses these problems with a remotely powered MR injector that efficiently utilizes AC electrical power provided at convenient AC outlets in a control room of an MRI suite.
- a remotely positioned power supply supplies the electrical power requirements for the entire MR injector system. Operators are no longer inconvenienced by charging and replacing batteries.
- installation of the MR injector system is enhanced by incorporating electrical power transmission into shielded electrical cables that also transmit data signals.
- a power supply outside of the shielded magnet room provides electrical power to a power head inside of the shielded magnet room via electrical cables coupled through a penetration panel.
- the power supply replaces a battery charger in an existing battery-powered injector system by providing electrical power across the penetration panel to a power control inside the shielded magnet room.
- the power control actuates a power head, which is near an MRI unit, to inject contrast agent and saline into patients undergoing an MRI scan.
- electrical power from an electrical cable from the penetration panel is interconnected with internal conductors of the power control that previously received power from a battery.
- the power supply is thus configured to provide electrical power equivalent to those of previously-used batteries.
- FIG. 1 is schematic of a prior art battery-powered injector installed in a magnetic resonance imaging (MRI) suite
- FIG. 2 is a schematic of a power injector consistent with the present invention with components installed in the magnet room directly powered by other components installed outside of the magnet room.
- a remotely powered MR injector system 50 consistent with the present invention is installed in an MRI suite 52 having a magnet room 54 enclosed within EMI shielded walls 56 .
- Other portions of the MRI suite 52 depicted as an equipment room 58 and a control room 60 , are electrically accessible to the magnet room 54 via a penetration panel 62 in the EMI shielded walls 56 .
- a power supply 64 of the system 50 advantageously provides electrical power to the entire system 50 , reaching portions of the system 50 within the magnet room 54 via the penetration panel 62 , thereby eliminating the need for battery power to power a power head 66 near an MRI unit 68 .
- the power supply 64 simplifies installation in the MRI suite 52 by accessing a standard AC outlet 70 in the control room 60 .
- the power supply 64 converts standard utility AC power from the outlet 70 into several forms suitable for the other major components of the system 50 with an AC-DC switcher 72 , such as a GPM225 global performance switcher available from Condor D.C. Power Supplies, Inc. of Oxnard, Calif.
- This AC-DC switcher 72 is suitable for use in a medical facility such as control room 60 and may be flexibly supplied from outlet power ranging from 28-264 Vac, 47-63 Hz single phase. Examples of alternative implementations of switcher 72 include the PM200 Series of AC-DC switching power supplies from International Power Sources, Inc. of Holliston, Mass.
- the power supply 64 advantageously emulates the power performance of the batteries installed into a conventional power control 74 in the magnet room 22 .
- a first electrical cable 76 outside of the magnet room 22 couples the power supply 64 to the penetration panel 62 .
- the first electrical cable includes data conductors 78 suitable for electronic data signals for sensing and command signals and power conductors 80 suitable for electrical power signals for powering electronics and electro-mechanical devices (e.g., ultrasonic motors of power head 66 ).
- the power conductors 80 may be coupled to the battery compartment 81 to utilize existing electrical power wiring in the power control 74 .
- the first cable 76 connects to a conventional RF filter 86 at the penetration panel 62 .
- the RF filter 86 grounds conductive shields of the first cable 76 so that induced noise on the shields is reduced at the EMI shielded wall 56 .
- the RF filter 86 attenuates RF noise on data and power conductors 76 , 80 within a rejection frequency band selected to correspond to the RF frequencies used by the MRI unit 68 .
- the other side of the penetration panel electrically couples to a second electrical cable 84 via a free hanging D-shell connector (not shown).
- the other end of the second cable 84 couples to the power control 74 .
- the second electrical cable 84 includes data conductors 88 suitable for electronic data signals for sensing and command signals and power conductors 90 suitable for electrical power signals for powering electronics and electro-mechanical devices.
- the power control 74 includes power head control electronics 92 that receives feedback and any operator commands input at the power head 66 .
- the power head control electronics 92 further provides operation status data to a touch-screen console 94 in the control room 60 for display to an operator.
- the power head control electronics 92 also receives commands from the console 94 and responds by activating a DC-AC ultra sonic motor drive 96 to produce a signal over a power head cable 98 to the power head 66 to actuate syringe plungers to dispense contrast media and/or saline solution.
- the power supply 64 facilitates communication between the console and power control 74 by including a data link 100 that couples the first cable 76 to a console cable 102 .
- the console cable 102 advantageously includes data conductors 104 for conducting data signals and power conductors 106 for powering the console 94 .
- the power supply 64 may include an interconnection between the AC power received from the AC outlet 70 to an AC outlet 108 externally mounted for a conventional electrical plug of a conventional monitor 94 .
- the data link 100 may further include an original equipment manufacturer (OEM) data port 110 for later upgrades to the system 50 .
- OEM original equipment manufacturer
- an operator of a remotely powered MR injector system 50 installs a console 94 and power supply 64 in a control room 60 of an MRI suite 52 by plugging the power supply 64 into an AC outlet 70 .
- a console cable 102 is connected between the console 94 and the power supply 64 .
- a power control 74 and a power head 66 are positioned within the magnet room 54 . Specifically, the power head 66 is placed proximate to the MRI unit 68 and connected via power head cable 98 to the power control 74 .
- the power control 74 is spaced away from the MR unit 68 .
- any ferromagnetic components of the power control 74 are not only shielded, but also oriented such that the entire power control 74 may be oriented with respect to the magnetic field from the MRI unit to minimize magnetic field interruption.
- Communication between the portions of the system in rooms 54 , 60 is facilitated by cables 76 , 84 between the power supply 64 and power control 74 .
- cables 76 , 84 include power conductors 80 , 90 to remotely power the power head 66 via power control 74 .
- an improved MR injector system 50 is operable within the demanding EMIC constraints of the MRI suite 52 without the inconvenience and additional costs of using battery power inside the magnet room 54 .
Abstract
A method of operation for a magnetic resonance imaging suite. A power supply of magnetic resonance injector system receives electrical power from an AC power outlet, both of which are located outside of a shielded room of the magnetic resonance imaging suite. Electrical power from the power supply of the magnetic resonance injector system is conveyed (via an appropriate power connection) into the shielded room of the magnetic resonance imaging suite and to a component (e.g., a power head) of the magnetic resonance injector system located inside the shielded room. While this electrical power is being conveyed, radio frequency energy emitted from the power connection is being filtered.
Description
- This application is a continuation of co-pending U.S. patent application Ser. No. 11/938,553 which is a continuation of co-pending U.S. patent application Ser. No. 09/851,462 filed on 8 May 2001 and entitled “Remotely Powered MR Injector”, now U.S. Pat. 7,512,434, the disclosure of both hereby incorporated by reference.
- The invention relates to contrast media power injectors compatible for use within a magnetic resonance imaging (MRI) suite, and in particular, to electrical interconnection of components of a magnetic resonance (MR) injector.
- A Magnetic Resonance Imaging (MRI) unit consists of a large cylindrical superconducting magnet for generating a strong magnetic field, devices for transmitting and receiving radio waves, and a complex computer system. When a patient lies inside the MRI unit, the strong magnetic field causes the hydrogen nuclei in the patient to line up. A low-frequency radio wave is pulsed through the magnet into the patient. The hydrogen atoms absorb the energy released by the radio waves. This disrupts the uniformity of the nuclei. When the radio-wave stimulation stops, the nuclei return to their original state and emit energy in the form of weak radio frequency (RF) signals. The strength and length of these RF signals—and therefore the kind of image produced—depend on the properties of the organ or tissue involved. A computer translates the RF signals into highly detailed cross-sectional images. The images are essentially maps of the locations of water or hydrogen in the body. The magnetic field produced by the MRI unit constrains installation of associated MRI equipment. In particular, any ferromagnetic object near the MRI unit will be attracted by the magnetic field, either impairing operation of the equipment or becoming a safety hazard if forcibly projected toward the MRI unit. Also, the uniformity of the magnetic field of the MRI unit is altered by ferromagnetic material, even if the ferromagnetic material is secured to prevent safety hazards. Consequently, ferromagnetic material is generally kept away from the MRI unit.
- The radio frequency transmissions emitted by the MRI unit toward the patient also poses electromagnetic interference/compatibility (EMIC) constraints on the installation of other equipment. General consumer and medical equipment such as personal computers and monitors are typically inadequately shielded to prevent impairment of function due to the strength of such RF emissions. Inversely, the MRI unit is susceptible to degraded performance if RF noise from other equipment distorts the received RF signal during imaging.
- For these reasons, the core of the MRI unit, including the magnetic field producing and RF transmission and receiving portions, is placed within a magnet room that is shielded from the other rooms of the MRI suite and the rest of the facility. Often, nonferrous metal sheets or mesh encompass the entire magnet room to prevent magnetic energy and RF energy from entering or leaving the magnet room. Consequently, the MRI unit generally includes highly shielded electrical power, data and control cabling that are routed through filtered and grounded access points so that susceptible or interfering components of the MRI unit may be placed outside of the shielded room.
- The same installation constraints affect installation of other equipment in the shielded magnet room. For example, utility electrical power, typically provided as AC outlets throughout the facility, is a transmission path for RF noise and is thus often not provided in the shielded magnet room. Similarly, sensors and controls for equipment used in the MRI suite often have to be placed in another room of the MRI suite, typically either an equipment room or control room. These controls are connected to the magnet room via a penetration panel that maintains the EMI shielding while allowing penetration by shielded and filtered electrical cables.
- As MRI units became capable of increased computational speed, opportunities were presented for use of contrast media, injected into patients before or during an MRI scan, to enhance dynamic imaging studies. In addition, contrast media were developed that allowed MRI scanning of certain types of tissues that otherwise were insufficiently distinguishable from surrounding tissue for effective MRI diagnostic studies. Power injectors for contrast media are sometimes preferred due to repeatability of dosage volumes and injection rates and keeping personnel away from the MRI unit during a scan. However, adapting contrast media injectors from other radiological modalities (e.g., X-ray, Computer-aided Tomography (CT), etc.) was difficult due to MRI unit installation limitations.
- With reference to
FIG. 1 , a power injector system 10 for injecting image-enhancing contrast media into a patient before or during an MRI scan is depicted as installed in anMRI suite 12. In particular, the power injector system 10 depicted is an OPTISTAR™ magnetic resonance (MR) digital injection system available from Mallinckrodt, Liebel-Flarsheim Business, Cincinnati, Ohio. The system 10 successfully operates within anMRI suite 12 by placement of components at varying distances from anMRI unit 14 or with varying degrees of shielding. In particular, apower head 16 contains ultrasonic motors. The ultrasonic motors operate syringes to dispense contrast media and saline solution into a patient as commanded and powered over a shieldedpower head cable 18 by apower control 20. - The
power control 20 is also within a shieldedmagnet room 22 of theMRI suite 12 along with thepower head 16 and theMRI unit 14, although generally spaced away from theMRI unit 14 to reduce the EMIC considerations. Since AC outlets are generally not available in the shieldedmagnet room 22, thepower control 20 is battery powered. Thepower control 20 provides power to thepower head 16 in response to data signals that are relayed from thepower head 16 to thepower control 20 and between thepower control 20 and a touch-screen console 24 outside of the shieldedmagnet room 22. In particular, a shieldedelectrical cable 26 for transferring data signals couples thepower control 20 to an opening, such as a free hanging D-shell connector 28, in apenetration panel 30. Anelectrical cable 32 outside of the shieldedmagnet room 22 is electrically coupled to the otherelectrical cable 26 inside the shieldedmagnet room 22 via afilter 34 connected to thepenetration panel 30. Thefilter 34 reduces RF noise induced on thecables MRI suite 12, thecable 32 passes from anequipment room 36 that is positioned adjacent to thepenetration panel 30 to a control room 38 where the MRI unit controls (not shown) and the power injector touch-screen console 24 reside. - Since the
power control 20, and thus thepower head 16, is battery powered, abattery charger 40 is placed in the control room 38 for recharging abattery 42 for use in thepower control 20. Thebattery charger 40 receives its power from an AC outlet 44. Thus, an inconvenient task is placed on operators of theMRI unit 14 and battery-powered injector system 10 to monitor the state of charge ofbatteries 42 and swap batteries between thebattery charger 40 and thepower control 20. If an undercharge ofbatteries 42 installed in thepower control 20 is not detected in a timely fashion, the operation of theMRI unit 14 is delayed, reducing the number of patients that may be scanned. Such reduction in the number of patients increases medical costs and limits delivery of medical services. - In addition to clinical and staffing considerations, there is the increased inventory of
batteries 42 necessary to have sufficient batteries for both use and simultaneous recharging. Furthermore, use of battery power places design constraints upon the battery-powered injector system 10, such as reducing functionality or increasing the size and cost of thebatteries 42 to handle the power demand. - As an example of a design constraint, the
power control 20 provides power for the electronic components and the ultrasonic motors of thepower head 16 and the electronic components of thepower control 20 itself. Thepower control 20 does not power components outside themagnet room 22. Consequently, several of the major components of the battery-powered injector system 10 each individually have internal power supplies that regulate and convert electrical power for use by that major component. For example, the console includes a power supply that also receives power from the AC outlet 44 and converts the AC electrical power to DC voltages useful for the electronics and display devices therein. Similarly, thebattery charger 40 includes an internal power supply that regulates and converts AC power to voltages suitable for its electronics and for thebattery 42 being recharged. Also, thepower control 20 includes an internal power supply for regulating and converting the battery power from installedbatteries 42 for the voltages required for its operation. Each internal power supply increases the cost, the size, and the cooling requirement of each major component. - Therefore, a significant need exists for an MR injector system with reduced cost that is simpler to operate than current battery-powered injector systems.
- The present invention addresses these problems with a remotely powered MR injector that efficiently utilizes AC electrical power provided at convenient AC outlets in a control room of an MRI suite. In particular, a remotely positioned power supply supplies the electrical power requirements for the entire MR injector system. Operators are no longer inconvenienced by charging and replacing batteries. In addition, installation of the MR injector system is enhanced by incorporating electrical power transmission into shielded electrical cables that also transmit data signals.
- In one particular aspect of the present invention, a power supply outside of the shielded magnet room provides electrical power to a power head inside of the shielded magnet room via electrical cables coupled through a penetration panel.
- In another aspect of the present invention, the power supply replaces a battery charger in an existing battery-powered injector system by providing electrical power across the penetration panel to a power control inside the shielded magnet room. The power control actuates a power head, which is near an MRI unit, to inject contrast agent and saline into patients undergoing an MRI scan. In particular, electrical power from an electrical cable from the penetration panel is interconnected with internal conductors of the power control that previously received power from a battery. The power supply is thus configured to provide electrical power equivalent to those of previously-used batteries. Thereby, existing MR injector systems receive many of the benefits provided by a remotely powered MR injector system.
- The above and other objects and advantages of the present invention shall be made apparent from the accompanying figures and the description thereof.
- The accompanying figures, which are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and, together with a general description of the invention given above, and the detailed description of the embodiments given below, serve to explain the principles of the invention.
-
FIG. 1 is schematic of a prior art battery-powered injector installed in a magnetic resonance imaging (MRI) suite; and -
FIG. 2 is a schematic of a power injector consistent with the present invention with components installed in the magnet room directly powered by other components installed outside of the magnet room. - Turning to
FIG. 2 , a remotely poweredMR injector system 50 consistent with the present invention is installed in anMRI suite 52 having amagnet room 54 enclosed within EMI shieldedwalls 56. Other portions of theMRI suite 52, depicted as anequipment room 58 and acontrol room 60, are electrically accessible to themagnet room 54 via apenetration panel 62 in the EMI shieldedwalls 56. Apower supply 64 of thesystem 50 advantageously provides electrical power to theentire system 50, reaching portions of thesystem 50 within themagnet room 54 via thepenetration panel 62, thereby eliminating the need for battery power to power apower head 66 near anMRI unit 68. - The
power supply 64 simplifies installation in theMRI suite 52 by accessing astandard AC outlet 70 in thecontrol room 60. In the illustrative embodiment, thepower supply 64 converts standard utility AC power from theoutlet 70 into several forms suitable for the other major components of thesystem 50 with an AC-DC switcher 72, such as a GPM225 global performance switcher available from Condor D.C. Power Supplies, Inc. of Oxnard, Calif. This AC-DC switcher 72 is suitable for use in a medical facility such ascontrol room 60 and may be flexibly supplied from outlet power ranging from 28-264 Vac, 47-63 Hz single phase. Examples of alternative implementations ofswitcher 72 include the PM200 Series of AC-DC switching power supplies from International Power Sources, Inc. of Holliston, Mass. - For an existing OPTISTAR™ MR system, the
power supply 64 advantageously emulates the power performance of the batteries installed into aconventional power control 74 in themagnet room 22. Specifically, a firstelectrical cable 76 outside of themagnet room 22 couples thepower supply 64 to thepenetration panel 62. The first electrical cable includesdata conductors 78 suitable for electronic data signals for sensing and command signals andpower conductors 80 suitable for electrical power signals for powering electronics and electro-mechanical devices (e.g., ultrasonic motors of power head 66). For instance, thepower conductors 80 may be coupled to thebattery compartment 81 to utilize existing electrical power wiring in thepower control 74. - The
first cable 76 connects to aconventional RF filter 86 at thepenetration panel 62. TheRF filter 86 grounds conductive shields of thefirst cable 76 so that induced noise on the shields is reduced at the EMI shieldedwall 56. Also, theRF filter 86 attenuates RF noise on data andpower conductors MRI unit 68. On the inside of themagnet room 54, the other side of the penetration panel electrically couples to a secondelectrical cable 84 via a free hanging D-shell connector (not shown). The other end of thesecond cable 84 couples to thepower control 74. Like thefirst cable 76, the secondelectrical cable 84 includesdata conductors 88 suitable for electronic data signals for sensing and command signals andpower conductors 90 suitable for electrical power signals for powering electronics and electro-mechanical devices. - It will be appreciated that additional interconnections may be made, such as wall connector (not shown) in the
wall 91 between theconsole room 60 and theequipment room 58. Similarly, instead of onecable major components system 50, a plurality of cables electrically run in parallel may be used. - The
power control 74 includes powerhead control electronics 92 that receives feedback and any operator commands input at thepower head 66. The powerhead control electronics 92 further provides operation status data to a touch-screen console 94 in thecontrol room 60 for display to an operator. The powerhead control electronics 92 also receives commands from theconsole 94 and responds by activating a DC-AC ultrasonic motor drive 96 to produce a signal over apower head cable 98 to thepower head 66 to actuate syringe plungers to dispense contrast media and/or saline solution. - The
power supply 64 facilitates communication between the console andpower control 74 by including adata link 100 that couples thefirst cable 76 to aconsole cable 102. Theconsole cable 102 advantageously includesdata conductors 104 for conducting data signals andpower conductors 106 for powering theconsole 94. Alternatively or in addition topower conductors 106, thepower supply 64 may include an interconnection between the AC power received from theAC outlet 70 to anAC outlet 108 externally mounted for a conventional electrical plug of aconventional monitor 94. The data link 100 may further include an original equipment manufacturer (OEM)data port 110 for later upgrades to thesystem 50. - In use, an operator of a remotely powered
MR injector system 50 installs aconsole 94 andpower supply 64 in acontrol room 60 of anMRI suite 52 by plugging thepower supply 64 into anAC outlet 70. Aconsole cable 102 is connected between theconsole 94 and thepower supply 64. Apower control 74 and apower head 66 are positioned within themagnet room 54. Specifically, thepower head 66 is placed proximate to theMRI unit 68 and connected viapower head cable 98 to thepower control 74. Thepower control 74 is spaced away from theMR unit 68. Ideally, any ferromagnetic components of thepower control 74 are not only shielded, but also oriented such that theentire power control 74 may be oriented with respect to the magnetic field from the MRI unit to minimize magnetic field interruption. Communication between the portions of the system inrooms cables power supply 64 andpower control 74. In addition,cables power conductors power head 66 viapower control 74. - By virtue of the foregoing, an improved
MR injector system 50 is operable within the demanding EMIC constraints of theMRI suite 52 without the inconvenience and additional costs of using battery power inside themagnet room 54. - While the present invention has been illustrated by a description of various embodiments and while these embodiments have been described in considerable detail, it is not the intention of the applicants to restrict or in any way limit the scope of the appended claims to such detail. Additional advantages and modifications will readily appear to those skilled in the art. The invention in its broader aspects is therefore not limited to the specific details, representative apparatus and method, and illustrative example shown and described. Accordingly, departures may be made from such details without departing from the spirit or scope of applicant's general inventive concept.
Claims (10)
1. A method of operation for an MR injector system, the method comprising:
a power supply of the injector system receiving AC power from an AC power outlet;
the power supply converting the AC power received to DC power;
conveying power from the power supply toward a battery compartment of the injector system;
filtering radio frequency energy from the power conveyed from the power supply toward the battery compartment of the injector system; and
conveying power from the battery compartment to a power head of the injector system.
2. The method of claim 1 , wherein the battery compartment is devoid of a battery during the conveying of power from the power supply toward the battery compartment.
3. The method of claim 1 , wherein the battery compartment is devoid of a battery during the conveying of power from the battery compartment to the power head.
4. The method of claim 1 , further comprising a power control that comprises the battery compartment.
5. The method of claim 1 , wherein the conveying of power from the power supply toward the battery compartment comprises the power being conveyed through a penetration panel of an MRI suite.
6. The method of claim 5 , wherein the filtering of radio frequency energy from the power conveyed from the power supply is accomplished at or near a penetration panel of an MRI suite.
7. The method of claim 6 , wherein the filtering occurs prior to the power being conveyed through the penetration panel.
8. The method of claim 5 , wherein the filtering comprises attenuating RF noise within a rejection frequency band selected to correspond to RF frequencies used by an MRI unit.
9. The method of claim 1 , further comprising:
transmitting data signals from a control panel of the injector system to a power head of the injector system.
10. The method of claim 1 , further comprising:
installing a syringe containing contrast media on the power head of the injector system, and
energizing said power head with power from the battery compartment to expel contrast media from said syringe.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US13/155,177 US20110237932A1 (en) | 2001-05-08 | 2011-06-07 | Method of Operation for a Magnetic Resonance Imaging Suite |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/851,462 US7512434B2 (en) | 2001-05-08 | 2001-05-08 | Remotely powered injector |
US11/938,553 US7991451B2 (en) | 2001-05-08 | 2007-11-12 | Method of operation for a magnetic resonance imaging suite |
US13/155,177 US20110237932A1 (en) | 2001-05-08 | 2011-06-07 | Method of Operation for a Magnetic Resonance Imaging Suite |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/938,553 Continuation US7991451B2 (en) | 2001-05-08 | 2007-11-12 | Method of operation for a magnetic resonance imaging suite |
Publications (1)
Publication Number | Publication Date |
---|---|
US20110237932A1 true US20110237932A1 (en) | 2011-09-29 |
Family
ID=25310817
Family Applications (4)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/851,462 Expired - Lifetime US7512434B2 (en) | 2001-05-08 | 2001-05-08 | Remotely powered injector |
US11/938,553 Expired - Fee Related US7991451B2 (en) | 2001-05-08 | 2007-11-12 | Method of operation for a magnetic resonance imaging suite |
US12/255,282 Expired - Fee Related US7772848B2 (en) | 2001-05-08 | 2008-10-21 | Method of operation for a magnetic resonance imaging suite |
US13/155,177 Abandoned US20110237932A1 (en) | 2001-05-08 | 2011-06-07 | Method of Operation for a Magnetic Resonance Imaging Suite |
Family Applications Before (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/851,462 Expired - Lifetime US7512434B2 (en) | 2001-05-08 | 2001-05-08 | Remotely powered injector |
US11/938,553 Expired - Fee Related US7991451B2 (en) | 2001-05-08 | 2007-11-12 | Method of operation for a magnetic resonance imaging suite |
US12/255,282 Expired - Fee Related US7772848B2 (en) | 2001-05-08 | 2008-10-21 | Method of operation for a magnetic resonance imaging suite |
Country Status (4)
Country | Link |
---|---|
US (4) | US7512434B2 (en) |
EP (1) | EP1386174A1 (en) |
JP (2) | JP2004533295A (en) |
WO (1) | WO2002091008A1 (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9660336B2 (en) | 2013-02-07 | 2017-05-23 | Kevan ANDERSON | Systems, devices and methods for transmitting electrical signals through a faraday cage |
US10578689B2 (en) | 2015-12-03 | 2020-03-03 | Innovere Medical Inc. | Systems, devices and methods for wireless transmission of signals through a faraday cage |
US11374646B2 (en) | 2017-05-09 | 2022-06-28 | Innovere Medical Inc. | Systems and devices for wireless communication through an electromagnetically shielded window |
Families Citing this family (25)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2002082113A2 (en) * | 2001-04-30 | 2002-10-17 | Medrad, Inc. | Improved mr injector system with increased mobility and electromagnetic interference mitigation |
US7512434B2 (en) * | 2001-05-08 | 2009-03-31 | Liebel-Flarsheim Company | Remotely powered injector |
US7361170B2 (en) * | 2001-11-21 | 2008-04-22 | E-Z-Em, Inc. | Device, system, kit or method for collecting effluent from an individual |
US7224143B2 (en) * | 2002-11-27 | 2007-05-29 | Medrad, Inc. | Continuous battery charger system |
JP4338447B2 (en) * | 2003-06-06 | 2009-10-07 | 株式会社根本杏林堂 | Chemical injection system |
WO2006000415A1 (en) * | 2004-06-24 | 2006-01-05 | E-Z-Em, Inc. | Hydraulic injection system and injection method |
US8900187B2 (en) * | 2004-10-13 | 2014-12-02 | Mallinckrodt Llc | Powerhead control in a power injection system |
US20060079842A1 (en) * | 2004-10-13 | 2006-04-13 | Liebel-Flarsheim Company | Powerhead control in a power injection system |
US7507221B2 (en) | 2004-10-13 | 2009-03-24 | Mallinckrodt Inc. | Powerhead of a power injection system |
EP1835871B1 (en) * | 2004-12-22 | 2013-05-22 | Bracco Diagnostics Inc. | System, imaging suite, and method for using an electro-pneumatic insufflator for magnetic resonance imaging |
US7806850B2 (en) | 2005-10-24 | 2010-10-05 | Bracco Diagnostics Inc. | Insufflating system, method, and computer program product for controlling the supply of a distending media to an endoscopic device |
US8294588B2 (en) * | 2006-05-12 | 2012-10-23 | Koninklijke Philips Electronics N.V. | Battery system for MRI compatible wireless patient monitor |
US8139948B2 (en) * | 2006-06-12 | 2012-03-20 | Acist Medical Systems, Inc. | Process and system for providing electrical energy to a shielded medical imaging suite |
EP2289581B1 (en) * | 2006-10-11 | 2013-11-06 | Mallinckrodt LLC | Injector having low input power |
JP5118895B2 (en) * | 2007-06-06 | 2013-01-16 | 株式会社根本杏林堂 | Electric medical system, power receiving medical unit and power transmission unit |
EP2209416A4 (en) | 2007-10-15 | 2014-05-14 | Univ Maryland | Apparatus and method for use in analyzing a patient's bowel |
WO2010021953A2 (en) | 2008-08-19 | 2010-02-25 | Mallinckrodt Inc. | Power injector with syringe communication logic |
EP2184615A1 (en) | 2008-11-05 | 2010-05-12 | Koninklijke Philips Electronics N.V. | A magnetic resonance imaging system comprising a power supply unit adapted for providing direct current electrical power |
ES2629012T3 (en) | 2009-07-24 | 2017-08-07 | Bayer Healthcare Llc | Multifluid medical injection system |
WO2011046857A1 (en) | 2009-10-15 | 2011-04-21 | Mallinckrodt Inc. | Piezoelectrically-driven power injector |
US8552725B2 (en) * | 2009-12-07 | 2013-10-08 | Northrop Grumman Guidance & Electronics Company, Inc. | Systems and methods for obstructing magnetic flux while shielding a protected volume |
BR112013012846B1 (en) | 2010-11-24 | 2020-12-08 | Bracco Diagnostics Inc | insufflation system |
IN2014CN02773A (en) * | 2011-10-25 | 2015-07-03 | Koninkl Philips Nv | |
RU2677925C1 (en) * | 2013-12-12 | 2019-01-22 | Конинклейке Филипс Н.В. | Method to enable standard alternating current/direct current power adapters to operate in high magnetic fields |
CN104791312B (en) * | 2015-03-03 | 2017-01-18 | 深圳圣诺医疗设备股份有限公司 | High-pressure injection system |
Citations (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4613820A (en) * | 1984-04-06 | 1986-09-23 | General Electric Company | RF shielded room for NMR imaging system |
US5432544A (en) * | 1991-02-11 | 1995-07-11 | Susana Ziarati | Magnet room display of MRI and ultrasound images |
US5573000A (en) * | 1992-11-17 | 1996-11-12 | Elscint Ltd. | Radio-frequency interference shield in MRI systems |
US5592030A (en) * | 1993-08-19 | 1997-01-07 | Adahan; Carmeli | Power supply for energizing DC load from AC or DC source |
US5877732A (en) * | 1994-04-13 | 1999-03-02 | Resonance Technology Co. | Three-dimensional high resolution MRI video and audio system and method |
USRE36648E (en) * | 1993-11-26 | 2000-04-11 | Medrad, Inc. | Patient infusion system for use with MRI |
US6198285B1 (en) * | 1997-11-28 | 2001-03-06 | Hitachi Medical Corporation | In-room MRI display terminal and remote control system |
US20010037063A1 (en) * | 2000-03-29 | 2001-11-01 | Albert Mitchell S. | Low-field MRI |
US20020169415A1 (en) * | 2001-05-08 | 2002-11-14 | Liebel-Flarsheim Company | Remotely powered injector |
US20030050555A1 (en) * | 2001-04-30 | 2003-03-13 | Critchlow Richard G. | MR injector system with increased mobility and electromagnetic interference mitigation |
US6590391B1 (en) * | 1998-09-17 | 2003-07-08 | Hitachi Medical Corporation | Mri diagnosis apparatus with an intergrated cabinet that is mechanically and electrically connected to the electrically conductive shield of the shield room in which the mr measurement system is arranged |
US6675037B1 (en) * | 1999-09-29 | 2004-01-06 | Regents Of The University Of Minnesota | MRI-guided interventional mammary procedures |
US20040197058A1 (en) * | 2001-07-26 | 2004-10-07 | Eric Eichelberger | High speed electronic remote medical imaging system and method |
US20050273000A1 (en) * | 2004-06-02 | 2005-12-08 | Dinehart William J | Method and apparatus for providing a stimulus in magnetic resonance imaging system |
US7267661B2 (en) * | 2002-06-17 | 2007-09-11 | Iradimed Corporation | Non-magnetic medical infusion device |
US20070285021A1 (en) * | 2006-06-12 | 2007-12-13 | E-Z-Em, Inc. | Process and system for providing electrical energy to a shielded medical imaging suite |
US7343191B1 (en) * | 2001-12-27 | 2008-03-11 | Fonar Corporation | MRI system |
Family Cites Families (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5530878A (en) | 1994-11-17 | 1996-06-25 | Sun Microsystems, Inc. | Simplified power system with a single power converter providing low power consumption and a soft on/off feature |
JP2790101B2 (en) | 1995-11-27 | 1998-08-27 | 東レ株式会社 | Particle aggregation pattern judgment device |
JP3578295B2 (en) | 1996-04-26 | 2004-10-20 | 株式会社日立メディコ | Open magnetic resonance imaging system |
US6752787B1 (en) | 1999-06-08 | 2004-06-22 | Medtronic Minimed, Inc., | Cost-sensitive application infusion device |
JP3557174B2 (en) * | 2000-05-02 | 2004-08-25 | 三鷹光器株式会社 | MRI microscope |
-
2001
- 2001-05-08 US US09/851,462 patent/US7512434B2/en not_active Expired - Lifetime
-
2002
- 2002-04-24 WO PCT/US2002/013282 patent/WO2002091008A1/en active Application Filing
- 2002-04-24 EP EP02729014A patent/EP1386174A1/en not_active Ceased
- 2002-04-24 JP JP2002588213A patent/JP2004533295A/en active Pending
-
2007
- 2007-11-12 US US11/938,553 patent/US7991451B2/en not_active Expired - Fee Related
-
2008
- 2008-04-25 JP JP2008116433A patent/JP2008188446A/en not_active Withdrawn
- 2008-10-21 US US12/255,282 patent/US7772848B2/en not_active Expired - Fee Related
-
2011
- 2011-06-07 US US13/155,177 patent/US20110237932A1/en not_active Abandoned
Patent Citations (24)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4613820A (en) * | 1984-04-06 | 1986-09-23 | General Electric Company | RF shielded room for NMR imaging system |
US5432544A (en) * | 1991-02-11 | 1995-07-11 | Susana Ziarati | Magnet room display of MRI and ultrasound images |
US5573000A (en) * | 1992-11-17 | 1996-11-12 | Elscint Ltd. | Radio-frequency interference shield in MRI systems |
US5592030A (en) * | 1993-08-19 | 1997-01-07 | Adahan; Carmeli | Power supply for energizing DC load from AC or DC source |
USRE36648E (en) * | 1993-11-26 | 2000-04-11 | Medrad, Inc. | Patient infusion system for use with MRI |
US5877732A (en) * | 1994-04-13 | 1999-03-02 | Resonance Technology Co. | Three-dimensional high resolution MRI video and audio system and method |
US6198285B1 (en) * | 1997-11-28 | 2001-03-06 | Hitachi Medical Corporation | In-room MRI display terminal and remote control system |
US6590391B1 (en) * | 1998-09-17 | 2003-07-08 | Hitachi Medical Corporation | Mri diagnosis apparatus with an intergrated cabinet that is mechanically and electrically connected to the electrically conductive shield of the shield room in which the mr measurement system is arranged |
US6675037B1 (en) * | 1999-09-29 | 2004-01-06 | Regents Of The University Of Minnesota | MRI-guided interventional mammary procedures |
US20010037063A1 (en) * | 2000-03-29 | 2001-11-01 | Albert Mitchell S. | Low-field MRI |
US6845262B2 (en) * | 2000-03-29 | 2005-01-18 | The Brigham And Women's Hospital, Inc. | Low-field MRI |
US20030050555A1 (en) * | 2001-04-30 | 2003-03-13 | Critchlow Richard G. | MR injector system with increased mobility and electromagnetic interference mitigation |
US20020169415A1 (en) * | 2001-05-08 | 2002-11-14 | Liebel-Flarsheim Company | Remotely powered injector |
US20080068011A1 (en) * | 2001-05-08 | 2008-03-20 | Liebel-Flarsheim Company | Method of Operation for a Magnetic Resonance Imaging Suite |
US7991451B2 (en) * | 2001-05-08 | 2011-08-02 | Liebel-Flarsheim Co. | Method of operation for a magnetic resonance imaging suite |
US7772848B2 (en) * | 2001-05-08 | 2010-08-10 | Liebel-Flarsheim Co. | Method of operation for a magnetic resonance imaging suite |
US7512434B2 (en) * | 2001-05-08 | 2009-03-31 | Liebel-Flarsheim Company | Remotely powered injector |
US20090045812A1 (en) * | 2001-05-08 | 2009-02-19 | Liebel-Flarsheim Company | Method of Operation for a Magnetic Resonance Imaging Suite |
US20040197058A1 (en) * | 2001-07-26 | 2004-10-07 | Eric Eichelberger | High speed electronic remote medical imaging system and method |
US6882785B2 (en) * | 2001-07-26 | 2005-04-19 | The Ludlow Company Lp | High speed electronic remote medical imaging system and method |
US7343191B1 (en) * | 2001-12-27 | 2008-03-11 | Fonar Corporation | MRI system |
US7267661B2 (en) * | 2002-06-17 | 2007-09-11 | Iradimed Corporation | Non-magnetic medical infusion device |
US20050273000A1 (en) * | 2004-06-02 | 2005-12-08 | Dinehart William J | Method and apparatus for providing a stimulus in magnetic resonance imaging system |
US20070285021A1 (en) * | 2006-06-12 | 2007-12-13 | E-Z-Em, Inc. | Process and system for providing electrical energy to a shielded medical imaging suite |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9660336B2 (en) | 2013-02-07 | 2017-05-23 | Kevan ANDERSON | Systems, devices and methods for transmitting electrical signals through a faraday cage |
US10578689B2 (en) | 2015-12-03 | 2020-03-03 | Innovere Medical Inc. | Systems, devices and methods for wireless transmission of signals through a faraday cage |
US11374646B2 (en) | 2017-05-09 | 2022-06-28 | Innovere Medical Inc. | Systems and devices for wireless communication through an electromagnetically shielded window |
Also Published As
Publication number | Publication date |
---|---|
WO2002091008A1 (en) | 2002-11-14 |
US7772848B2 (en) | 2010-08-10 |
US7512434B2 (en) | 2009-03-31 |
JP2008188446A (en) | 2008-08-21 |
EP1386174A1 (en) | 2004-02-04 |
JP2004533295A (en) | 2004-11-04 |
US20020169415A1 (en) | 2002-11-14 |
US20080068011A1 (en) | 2008-03-20 |
US20090045812A1 (en) | 2009-02-19 |
US7991451B2 (en) | 2011-08-02 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7991451B2 (en) | Method of operation for a magnetic resonance imaging suite | |
EP0655220B2 (en) | Magnetic resonance imaging system | |
US5432544A (en) | Magnet room display of MRI and ultrasound images | |
US11061089B2 (en) | System and methods for grounding patients during magnetic resonance imaging | |
US10653828B2 (en) | Sealed infusion device with electrical connector port | |
US6936030B1 (en) | Injector systems incorporating a base unit attached to a surface | |
JP2003534859A (en) | Communication system used for magnetic resonance imaging system | |
US10247791B2 (en) | System for converting audio signals to wireless audio signals in a medical imaging environment | |
US20110172525A1 (en) | Inductively Coupled Injector Faceplate | |
US8073524B2 (en) | Control of magnetic field homogeneity in movable MRI scanning system | |
EP3503860A1 (en) | Devices and methods for a neonate incubator, capsule and cart | |
CN101522238A (en) | Injector having low input power | |
JP4238264B2 (en) | Chemical solution injection device and fluoroscopic imaging device | |
WO2022258028A1 (en) | Magnetic resonance compatible robot system | |
US20100090699A1 (en) | Power supply for rf coils | |
KR20210095606A (en) | A control method of an electroceuticals for the treatment of epilepsy with an electromagnetic disturbance prevention function | |
WO2016100451A1 (en) | Systems and methods for energizing magnets of magnetic resonance imaging (mri) systems | |
WO2018026998A1 (en) | Electronic tablet for use in functional mri | |
WO2007095534A1 (en) | Medical imaging system having an integrated injection device | |
US20190223836A1 (en) | Ultrasound diagnostic apparatus and external battery unit thereof | |
JP2003325471A (en) | Magnetic resonance imaging apparatus | |
JP2020054856A (en) | Magnetic resonance imaging system | |
CA3032513A1 (en) | Support for an electronic tablet for use in functional mri |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: LIEBEL-FLARSHEIM COMPANY, OHIO Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:STAATS, PETER;KNIPFER, JAMES E.;SIGNING DATES FROM 20010503 TO 20010504;REEL/FRAME:028109/0636 |
|
AS | Assignment |
Owner name: LIEBEL-FLARSHEIM COMPANY LLC, MISSOURI Free format text: CHANGE OF LEGAL ENTITY;ASSIGNOR:LIEBEL-FLARSHEIM COMPANY;REEL/FRAME:028436/0103 Effective date: 20110623 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |