|Publication number||US3720199 A|
|Publication date||13 Mar 1973|
|Filing date||14 May 1971|
|Priority date||14 May 1971|
|Also published as||CA990802A1, DE2221417A1, DE2221417B2, DE2221417C3|
|Publication number||US 3720199 A, US 3720199A, US-A-3720199, US3720199 A, US3720199A|
|Inventors||Federico A, Rishton M|
|Original Assignee||Avco Corp|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (5), Non-Patent Citations (1), Referenced by (157), Classifications (16), Legal Events (1)|
|External Links: USPTO, USPTO Assignment, Espacenet|
United States Patent Rishton et al.
[ 51March 13, 1973  SAFETY CONNECTOR FOR BALLOON OTHER PUBLICATIONS PUMP Madras et al. Effects of Prolonged Intra-Aortic Bal-  Inventors: Michael L. Rishton, Reading; Arloon Pumping" Trans. Amer. Soc. Artif. lnt. Orgs.,
mando Federico, Needham, both of Vol. XV, 1969 pp. 400-405. Mass.
Primary ExaminerDalton L. Truluck  Asslgnee' Avco Corporation Cmcmnan Ohm Attorney-Charles M. Hogan and Melvin E. Frederick  Filed: May 14, 1971  Appl. No.: 143,392  ABSTRACT An intra aortic balloon catheter assembly for use in a Y circulatory assist system which includes a special con-  US. Cl. ..128/1 D, 128/214 R Hector forjoining a balloon implanted in the patientm  it. Cl. 19/00 a control console which y house both pneumatic  F'eld 1 214 273 and electronic controls. The connector is adapted to provide a signal which indicates volumetric displace- References C'ted ment of the balloon. This volume is compared to the UNITED STATES PATENTS volume of load gas utilized and shuts the system down if an over-inflation condition exists, prevents overm- 3,601,124 8/1971 Petree ..128/214E flation of the balloon, inadvertent use of an incor- 3,450,153 6/1969 Hildebrandt et al. ..128/214 E rectly sized balloon, and allows presterilization of the 3,465,746 9/1969 Guarino ..128/1 D whole assemb] 3,585,983 6/1971 Kantrowitz et al. ..128/] D y 3,457,909 7/1969 Laird ..128/1 D 6 Claims, 3 Drawing Figures are 57 LOAD 5 SUPPLY ISOLATION P egg/5 PISTON R 240 I SUPPLY \1\ PATIENT PULSE VALVE R l x EXHAUST PRESSURE 56 59 SUPPLY 55 9 PRESSURE VENT TRANSDUCER VALVE FROM 50 5| COMPARATOR 5 5 CG PUT '9 R WAVE DELAY 8i EXHAUST E DETECTOR TIME GENERATOR PATENTEDHAR] 31m SHEET 10F 2 V SfiV E 51 LOAD %g; 54 SUPPLY ISOLATION PR E S ERE PISTON N24 240 SUPPLY 1' PATIENT PULSE L VALVE EXHAUST 25 PRESSURE 56 59 SUPPLY 1.55 9 9 PRESSURE VENT TRANSDUCER VALVE FROM 50 5| COMPARATOR 5 i 2| RWAVE DELAYBlEXHAUST ECG DETECTOR TIME GENERATOR MICHAEL L. RISHTON ARMANDO FEiD ERICO 1N VENTOR.
ATTORNEYS PATEIIIEUIIARISISYS 720,199
SHEET 2 OF 2 114x420 svsnsrr RES LAB TO VENT I: VALVE CIRCUIT 59 1",
TO BALLOON v j I 5 AND PATIENT lj MICHAEL L. RISHTON ARMANDO F'EDERICO INVENTOR.
MWZA ATTORNEYS SAFETY CONNECTOR FOR BALLOON PUMP This invention relates to circulatory assist systems and in particular to an intra aortic balloon catheter assembly. This catheter assembly increases the safety performance of circulatory assist devices and, therefore, enhances the utilization of such implantable systems in the human body.
As is well known, the systemic circulation is maintained by the action of the left ventricle in pumping blood into the aorta. Back-flow of blood into the left ventricle is prevented by the aortic valve. During its contraction (systole) the left ventricle works primarily against the elastic compliance of the aorta, raising the pressure in the aorta and distending it. As soon as contraction is complete and the ventricle relaxes, the aortic valve closes and the elastic contraction of the aorta then maintains a continuing flow of blood through the capillaries and other vessels (diastole). In addition to its function as a vessel for carrying blood to various organs, the aorta thus acts as an elastic reservoir storing some of the energy supplied by the heart.
Situations are encountered in the treatment of heart disease where the patientsheart action is simply not sufficient to supply bodily needs. For example, weakness in the heart action called heart failure may occur following a myocardial infarct. Such a heart failure will exhibit low blood pressure during the systole cycle of the normal heart rhythm. This low blood pressure in turn reduces coronary blood flow, thereby, reducing further the blood pressure, creating adeteriorating cycle. It is envisioned that a mechanical device may be used to assist the circulation. I-Ieretofore, mechanical assistance to the systemic circulation has been attempted by veno-arterial pumping, arterio-arterio pumping, and a variety of counter-pulsation techniques have fallen short of certain desirable requirements,
thereby failing in complete acceptance; These proposals have proved too difficult, delicate and/or uncertain to maintain reliable operation, or they have proved to be partially impractical in fulfilling requirements of either proper relationship with natural heart action or volumetric response to desirable standards. Other proposals and/or related equipment have failed to respond to minimum standards of adjustability to meet adequately the requirements of the cardiac specialist.
From the foregoing discussion it will be clear then that the present invention provides an improvement over prior devices and will fill a long needed requirement in the field of circulatory assist blood systems. intra arterial or ballon" type pumps per se, for use, for example, in the aorta by insertion through the femoral artery, up the arterial tree and into the aorta, are well known. However, the operation, of the pump is extremely critical since it must operate periodically in a transient or instantaneous pulsating manner which must be synchronized with the patients heart. Furthermore, the stroke of such a pump must operate under various types of conditions such as at a different pressure relating to the pressure of the: patient.
The present invention assists 11C operation of such a system by providing means which will prevent the overinflation of the balloon pump. It is absolutely essential to the operation of any medical device used within the human body, that the device must be constructed as to prevent any forseeable hazards. Therefore, if a balloon is inserted and is overinflated because it is erroneously thought to be a larger balloon, the balloon may rupture or break in the patients circulatory system expelling injurious if not lethal amounts of gas into the blood stream. The above situation is prevented in accordance with the present invention by means of an electronic indicator. This indicator provides a signal to the control mechanism which in turn limits the amount of pressure provided to inflate the balloon.
An object of the present invention is to provide a safety mechanism for cardiac assist devices.
Another object of the invention is to prevent overinflation of balloon pump systems.
Another object of the invention is to provide an electronic indicator which may be used to determine the size of the balloon inserted into the aorta.
Still another object of the invention is to provide an intra aortic balloon catheter assembly which is an integrated system that may be presterilized as a unit.
A further object of this invention is to provide an intra aortic balloon assembly that iselectrically connected to the pneumatic systems.
Yet another object of the invention is to provide a mechanical safety connection between the balloon pump assembly and the balloon pump console.
The novel features that are considered characteristic of the invention are set forth in the appended claims, the invention itself, however, both as to its organization and its method of operation, together with additional objects and advantages, thereof, will best be understood from the following description of a specific embodiment when read in conjunction with the accompanying drawings in which:
FIG. 1 shows an overall view of an intra aortic balloon pump in accordance with the invention emplaced in a patient; a
FIG. 2 shows an expanded break away view of the safety connector, related electronics, and the balloo n pump console; and
FIG. 3 is a block diagram of the principal components of the balloon pump. console.
PREFERRED EMBODIMENT Attention is directed to FIGS. 1 and 2 which illustrate by way of example a preferred embodiment of the invention. FIG. 1 illustrates the use of a balloon pump system in accordance with the invention as used in a patient with. a cardiac condition. The balloon 15 which by way of example, as that described in U.S. Pat. No. 3,504,662 is introduced through the femoral artery and positioned. in the descending aorta of the patient. To facilitate the. insertion, the balloon is inserted in a deflated condition. the size of the balloon used with a particular patient is determined by the patients sex,
age, size. and general condition of health. Typical sizes which are used include ballons having a 20cc, 30cc, or 40cc volumetric displacement. The balloon is attached to a conventional hollow catheter 16 which provides a channel for coupling fluid such as for example, helium from the pumping console to the balloon to inflate and deflate the implanted balloon during operation. The end of the catheter 16 remote from the balloon is coupled to the electronics and pneumatics of the console 17 by the use of a special plug/socket type connection generally designated 18 which will be discusSed more fully hereinafter. The balloon, catheter, and part of the connector make up an integral, replaceable unit which may be sterilized together prior to insertion into the human body. The patients electrocardiac output (ECG) may for example, be monitored in the conventional manner via leads 19. The ECG signal is used in providing the timing sequence for the cardiac assist device so that the balloon will be inflated during the cardiac diastole period.
The basic function of a typical console is to provide inflation of the balloon following closure of the aortic valve on the next heartbeat. A typical block diagram of the principal components is shown in FIG. 3. The ECG signal is fed into a R-wave detector 50. The ECG signal consists of a scintilation pattern dependent upon the electrocardiac output, the highest positive going spiked portion of this signal occurs when the depolarization signal reaches the bundle of His in the heart prior to ventricular contraction. This positive spiked portion of the signal is known in electrocardiography as the R- wave which is sensed by the detector 50. Each R-wave signal from detector 50 is fed to delay and exhaust time generator 51 which provides electrical signal to electromechanical pulse valve 52. The R-wave starts a clock in the delay and exhaust time generator 51 from which the time of inflation an: deflation is measured. These times can be adjusted as fractions of the period between heartbeats by manual adjustments. The electrical signals from generator 51 for inflation or deflation actuate a conventional pulse valve 52 which connects the console side 24a of the isolating piston 24 to the drive pressure supply 54 or the exhaust pressure supply 55 respectively.
The isolating piston is used for safety purposes. It is designed so that it does not noticeably decrease the rate of inflation or deflation of the balloon. The isolating piston 24 separates the fluid in the drive mechanism on the console side 24a from the fixed amount of fluid or load gas on the patient side 24b used to inflate the balloon 15. Thus, in the unlikely event of a violent rupture of the balloon, only a limited amount of gas will be injected into the patient. Furthermore, small leaks in the balloon can be detected by the observation of a gradual drop in pressure of gas as measured by pressure transducer 56 on the patient side 24b of the isolating piston 53. Some replacement of load gas is normally required due to permeability of the balloon membrane to helium which is normally used as a load gas. Load gas may be replaced through a load valve 57 from a load supply 58. A vent valve 59 is provided on the patient side of the isolating piston which opens automatically in case of a circuit failure or the like and leaves the balloon in a deflated position.
Attention is now again directed to FIGS. 1 and 2. On the front of the console as best shown in FIG. 2, is positioned an isolating piston control knob 20 for affecting control of the isolating piston 24 in the fixed volume pump 25 to provide a desired volume of the gas in the patient side of the pump 24b which determines the amount of load gas to be used. The position of control knob 20 also provides an electrical signal by means of a potentiometer 26 that is fed to a conventional comparator 21 and an indicator 22 on the face of the console. The control knob 20 is initially set according to a volume of less than or equal to the specified volumetric capacity of the balloon and its associated catheter. When control knob 20 is positioned correctly, the volume reading at indicator 22 should not exceed the rated capacity of the balloon by more than 2cc. Allowing too large a displacement of the fixed volume pump can overpressure the balloon. A meter reading more than about Sccs lower than the rated balloon volume should be avoided since this indicates that part of the balloon is not inflating and is then subject to possible thrombotic complications. A balloon which does not fully inflate provides crevices which allow blood to stagnate and form clots which may impede flow and endanger the patient.
The mechanical connector 18 between the catheter and the console is shown in greater detail in FIG. 2. As shown in FIG. 2, the connector 18 comprises a male type plug 30 permanently affixed to the balloon catheter 16, and a female type socket 40 attached to the catheter leading to the console. Disposed within the plug 30 is a resistor 31. The valve of resistor 31 is chosen to reflect the volumetric displacement of the balloon 15 to which plug 30 is attached. Resistor 31 is electrically connected between pins 32 and 33 which are carried by plug 30. Catheter 16 is permanently and sealably connected to a rigid hollow tube 34 which is affixed to and protrudes a distance from the end surface of plug 30.
The female socket 40 is constructed as to receive plug 30, electrical insets 41 and 42 being adapted to receive pins 32 and 33 and recess 43 being adapted to sealably receive tube 34. Recess 43 receives tube 34 with an air tight connection when plug 30 is mated with socket 40. Recess 43 is permanently and sealably affixed to hollow tubinG 44 and which is removably connected to the fixed volume pump 25. This completes the pneumatic channel between the balloon and the console. Insets 41 and 42 receive pins 32 and 33 when plug 30 is mated with socket 40. The electrical inset 42 may provide for example, an electrical connection to ground, and electrical inset 41 may be electrically connected to comparator 21 contained within the consOle 17.
It will now be clear, therefore, than when plug 30 is mated to socket 40 an electrical circuit is completed between the comparator 21, resistor 31, and ground. As illustrated in FIG. 2, this circuit provides in conventional manner in comparator 21 a DC level based on resistor 31 which in turn is proportional to the size of the balloon being used. The comparator in conventional manner compares the aforementioned DC level with the signal provided by the manual volume load adjusting mechanism for the isolating piston. If the volume of the load gas to be provided to the balloon exceeds the safety limits of the balloon, the comparator provides a signal operative to shut off the operation of the volume meter and rapidly vent the system to the atmosphere. By way of example, this may be accomplished by providing a signal from comparator 21 to activate vent valve 59. This will immediately deflate the balloon and minimize the resistance to blood flow through the aorta. However, if the volume of the load gas to be provided to the balloon is within the safety limits of the balloon assembly, no shut down signal is generated to shut the operation off and the system may function safely in its normal mode.
The value of resistor 31 used in the circuit is matched to the volume of the balloon 15, thus, for example, a 30cc balloon may have a 510 ohm resistor and, a 20cc balloon may have a 300 ohm resistor. The circuit which is completed should be a low voltage (e.g., 2 volts) circuit in order to protect the patient from any electrical shock. Accordingly, only low impedence is necessary to complete the circuit through the resistor 31.
The various features and advantages of the invention are thought to be clear from the foregoing description. Various other features and advantages not specifically enumerated will undoubtedly occur to those versed in the art, as likewise will many variations and modifications 0F the preferred embodiment illustrated, all of which may be achieved without departing from the spirit and scope of the invention as defined by the following claims:
1. In a circulatory assist system having pneumatic means including pneumatic pump means adapted to sequentially apply pressure to a load gas to inflate and deflate a balloon placed in an artery of a patient, means for providing a first output signal proportional to the volumetric displacement of said pneumatic pump means, and electronic timing means for controlling said pneumatic means by sequencing said inflation and deflation to the said patients heart rhythm, the improvement comprising:
a. a catheter;
b. a balloon coupled to one end of said catheter, said balloon being adapted to be placed in an artery;
first means for providing a second output signal proportional to the volumetric displacement of said balloon, said first means comprising a connector for removeably coupling said catheter to said pneumatic pump means, said connector comprising first and second separable portions, said first portion being fixedly attached to the end of said catheter remote from said balloon, and impedance means carried by said first portion;
d. comparator means for receiving said first and second output signals and generating a third output signal when said first output signal is greater than said second output signal; and
e. venting means actuated by said third output signal for deactivating said pneumatic means.
2. The device of claim 1 wherein said first portion includes terminal means for electrically connectlng said impedance means in circuit with said comparator means, said first portion including further means for coupling said load gas to said balloon via said catheter.
3. The device of claim 2 additionally including tube means connected between said second portion and said pneumatic pump means whereby said load gas may inflate and deflate said balloon.
4. The device of claim 3 additionally including insets disposed in said second portion for receiving said ter-' minal means.
5. The device of claim 4 additionally including conductors electrically coupled to said insets for providing electrical connection between said insets and said comparator.
6. The device of claim 1 wherein the said impedance means is a resistor.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3450153 *||26 Jun 1967||17 Jun 1969||Gen Electric||Electrical pulse generator and regulator for fluid flow and like control systems|
|US3457909 *||20 Jul 1966||29 Jul 1969||Avco Corp||Heart augmentation system provided with means for measuring intra-arterial pressure|
|US3465746 *||2 Mar 1966||9 Sep 1969||Avco Corp||Monitor for heart pump apparatus|
|US3585983 *||5 Mar 1968||22 Jun 1971||Kantrowitz Adrian||Cardiac assisting pump|
|US3601124 *||29 Aug 1968||24 Aug 1971||Petree Frank L||Fluid flow regulator|
|1||*||Madras et al. Effects of Prolonged Intra Aortic Balloon Pumping Trans. Amer. Soc. Artif. Int. Orgs., Vol. XV, 1969 pp. 400 405.|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3918459 *||16 Jan 1974||11 Nov 1975||Sybron Corp||Constant current electrotherapy device with plug-in current control means|
|US3974825 *||1 Oct 1975||17 Aug 1976||Baylor College Of Medicine||Remote electrical monitoring of gas activated blood pumps|
|US3985123 *||17 Jul 1975||12 Oct 1976||Avco Everett Research Laboratory, Inc.||Method and means for monitoring cardiac output|
|US4004298 *||31 Mar 1975||25 Jan 1977||Sinai Hospital Of Detroit||Magnetically aligned releasable connector|
|US4051841 *||9 Oct 1975||4 Oct 1977||Thoma Dipl Ing Dr Techn Herwig||Method of and apparatus for automatically controlling heart-synchronized circulating pumps|
|US4369530 *||19 May 1981||25 Jan 1983||Foxcroft Associates||Hydraulically actuated cardiac prosthesis and method of actuation|
|US4376312 *||19 May 1981||15 Mar 1983||Foxcroft Associates||Hydraulically actuated cardiac prosthesis|
|US4381567 *||15 Sep 1981||3 May 1983||Foxcroft Associates||Hydraulically actuated total cardiac prosthesis with reversible pump and three-way ventricular valving|
|US4389737 *||15 Sep 1981||28 Jun 1983||Foxcroft Associates||Hydraulically actuated cardiac prosthesis with three-way ventricular valving|
|US4397049 *||15 Sep 1981||9 Aug 1983||Foxcroft Associates||Hydraulically actuated cardiac prosthesis with three-way ventricular valving|
|US4407298 *||16 Jul 1981||4 Oct 1983||Critikon Inc.||Connector for thermodilution catheter|
|US4439186 *||17 Aug 1982||27 Mar 1984||Adolf Kuhl||Dilation device|
|US4621643 *||5 Feb 1986||11 Nov 1986||Nellcor Incorporated||Calibrated optical oximeter probe|
|US4700708 *||26 Sep 1986||20 Oct 1987||Nellcor Incorporated||Calibrated optical oximeter probe|
|US4770179 *||19 Oct 1987||13 Sep 1988||Nellcor Incorporated||Calibrated optical oximeter probe|
|US4771765 *||16 Dec 1985||20 Sep 1988||Choy Daniel S J||Heart assist device and method of use|
|US4793351 *||15 Jun 1987||27 Dec 1988||Mansfield Scientific, Inc.||Multi-lumen balloon catheter|
|US4840066 *||27 Jun 1988||20 Jun 1989||Ndt Instruments, Inc.||Ultrasonic thickness gauge having automatic transducer recognition and parameter optimization and method thereof|
|US4858615 *||29 Jul 1988||22 Aug 1989||Sentron V.O.F.||Catheter sensor and memory unit|
|US4902273 *||22 Mar 1988||20 Feb 1990||Choy Daniel S J||Heart assist device|
|US4974774 *||4 Aug 1988||4 Dec 1990||Aisin Seiki Kabushiki Kaisha||Medical appliance driving apparatus|
|US5007898 *||2 Jun 1988||16 Apr 1991||Advanced Surgical Intervention, Inc.||Balloon dilatation catheter|
|US5011468 *||16 Apr 1990||30 Apr 1991||Retroperfusion Systems, Inc.||Retroperfusion and retroinfusion control apparatus, system and method|
|US5021046 *||10 Aug 1988||4 Jun 1991||Utah Medical Products, Inc.||Medical pressure sensing and display system|
|US5030227 *||1 Jun 1989||9 Jul 1991||Advanced Surgical Intervention, Inc.||Balloon dilation catheter|
|US5045051 *||14 Mar 1989||3 Sep 1991||Abiomed, Inc.||Leak detector|
|US5057120 *||28 Dec 1988||15 Oct 1991||Farcot Jean Christian||Apparatus for the performance of an angioplasty of long duration|
|US5059167 *||14 May 1990||22 Oct 1991||Retroperfusion Systems, Inc.||Retroperfusion and retroinfusion control apparatus, system and method|
|US5163904 *||12 Nov 1991||17 Nov 1992||Merit Medical Systems, Inc.||Syringe apparatus with attached pressure gauge|
|US5196017 *||15 Apr 1991||23 Mar 1993||Silva Fidel H||Method and apparatus for patient protection against vessel rupture from balloon-tipped catheters|
|US5201753 *||4 Mar 1991||13 Apr 1993||Merit Medical Systems, Inc.||Totally self-contained, digitally controlled, disposable syringe inflation system, and method for monitoring, displaying and recording balloon catheter inflation data|
|US5242374 *||27 Mar 1992||7 Sep 1993||Aisin Seiki Kabushiki Kaisha||Leak detector for an intra-aortic balloon pump|
|US5259838 *||18 Jun 1992||9 Nov 1993||Merit Medical Systems, Inc.||Syringe apparatus with attached pressure gauge and timer|
|US5273537 *||6 Mar 1992||28 Dec 1993||Scimed Life Systems, Inc.||Power-assisted inflation apparatus|
|US5300027 *||18 Mar 1992||5 Apr 1994||Merit Medical Systems, Inc.||System and method for monitoring and displaying balloon catheter inflation and deflation data|
|US5312430 *||28 Jun 1991||17 May 1994||Rosenbluth Robert F||Balloon dilation catheter|
|US5342298 *||31 Jul 1992||30 Aug 1994||Advanced Cardiovascular Systems, Inc.||Automated fluid pressure control system|
|US5380267 *||18 Jun 1993||10 Jan 1995||Datascope Investment Corp.||Noise-attenuating pneumatic compressor and medical apparatus incorporating same|
|US5383855 *||20 Aug 1992||24 Jan 1995||Medex, Inc.||Electronically monitored angioplasty system|
|US5385549 *||4 Mar 1993||31 Jan 1995||Merit Medical Systems, Inc.||Digitally controlled, disposable syringe inflation system, and method for monitoring, displaying balloon catheter inflation data|
|US5405269 *||26 Feb 1993||11 Apr 1995||Stupecky; Josef J.||Disposable electro-fluidic connector with data storage|
|US5425713 *||4 Apr 1994||20 Jun 1995||Merit Medical Systems, Inc.||System and method for monitoring, displaying and recording balloon catheter condition interval and inflation location data|
|US5431629 *||4 Apr 1994||11 Jul 1995||Merit Medical Systems, Inc.||System and method for monitoring, displaying and recording balloon catheter condition interval data|
|US5449344 *||5 Nov 1993||12 Sep 1995||Merit Medical Systems, Inc.||Syringe apparatus with pressure gauge and detachable timer|
|US5449345 *||30 Mar 1994||12 Sep 1995||Merit Medical Systems, Inc.||Detachable and reusable digital control unit for monitoring balloon catheter data in a syringe inflation system|
|US5453091 *||5 Apr 1994||26 Sep 1995||Merit Medical Systems, Inc.||RF transmission module for wirelessly transmitting balloon catheter data in a syringe inflation system|
|US5458571 *||4 Apr 1994||17 Oct 1995||Merit Medical Systems, Inc.||System and method for monitoring, displaying and recording balloon catheter condition interval data|
|US5459700 *||22 Nov 1993||17 Oct 1995||Advanced Cardiovascular Systems, Inc.||Manual timer control for inflation device|
|US5460609 *||22 Nov 1993||24 Oct 1995||Advanced Cardiovascular Systems, Inc.||Electromechanical inflation/deflation system|
|US5472424 *||5 Apr 1994||5 Dec 1995||Merit Medical Systems, Inc.||Syringe with volume displacement apparatus|
|US5484385 *||21 Apr 1994||16 Jan 1996||C. R. Bard, Inc.||Intra-aortic balloon catheter|
|US5513956 *||14 Jan 1994||7 May 1996||Arrow International Investment Corp.||Circulatory assisted device with motor driven gas pump|
|US5527336 *||2 Mar 1995||18 Jun 1996||Boston Scientific Corporation||Flow obstruction treatment method|
|US5545122 *||12 Oct 1994||13 Aug 1996||Spruill; Theresa||Inflatable speculum|
|US5562614 *||22 Nov 1993||8 Oct 1996||Advanced Cardiovascular Systems, Inc.||Programmable manifold system for automatic fluid delivery|
|US5562621 *||22 Nov 1993||8 Oct 1996||Advanced Cardiovascular Systems, Inc.||Communication system for linking a medical device with a remote console|
|US5588438 *||7 Jun 1995||31 Dec 1996||Interflo Medical, Inc.||System and method for controlling the temperature of a catheter-mounted heater|
|US5599301 *||22 Nov 1993||4 Feb 1997||Advanced Cardiovascular Systems, Inc.||Motor control system for an automatic catheter inflation system|
|US5704913 *||19 May 1994||6 Jan 1998||Boston Scientific Corporation||Dilation catheter and method of treatment therewith|
|US5720293 *||18 May 1994||24 Feb 1998||Baxter International Inc.||Diagnostic catheter with memory|
|US5752971 *||5 Jun 1995||19 May 1998||Boston Scientific Technology, Inc.||Method of treating a flow obstruction|
|US5807269 *||7 Jun 1995||15 Sep 1998||Baxter International Inc.||Thermodilution catheter having a safe, flexible heating element|
|US5836951 *||7 Jun 1995||17 Nov 1998||Boston Scientific Corporation||Balloon dilation catheter|
|US5857976 *||7 Jun 1995||12 Jan 1999||Baxter International Inc.||Thermodilution catheter having a safe, flexible heating element|
|US6042532 *||9 Mar 1998||28 Mar 2000||L. Vad Technology, Inc.||Pressure control system for cardiac assist device|
|US6048330 *||2 May 1997||11 Apr 2000||Children's Medical Center Corporation||Systems and methods for promoting tissue growth|
|US6082105 *||20 Nov 1996||4 Jul 2000||Nippon Zeon Co., Ltd.||Drive device for medical appliances|
|US6132363 *||30 Sep 1998||17 Oct 2000||L.Vad Technology, Inc.||Cardiovascular support control system|
|US6287275||11 Jan 1999||11 Sep 2001||Children's Medical Center Corporation||Systems and methods for promoting tissue growth|
|US6290641 *||20 May 1999||18 Sep 2001||Datascope Investment Corp.||Intra-aortic balloon pump having improved automated electrocardiogram based intra-aortic balloon deflation timing|
|US6351658||28 Sep 1999||26 Feb 2002||Mallinckrodt, Inc.||Multiple-code oximeter calibration element|
|US6355001||13 May 1996||12 Mar 2002||Edwards Lifesciences Corporation||Thermodilution catheter method using a safe, flexible heating element|
|US6356774||28 Sep 1999||12 Mar 2002||Mallinckrodt, Inc.||Oximeter sensor with encoded temperature characteristic|
|US6387052||19 Apr 1993||14 May 2002||Edwards Lifesciences Corporation||Thermodilution catheter having a safe, flexible heating element|
|US6432081||28 Mar 2000||13 Aug 2002||Children's Medical Center Corporation||Systems and methods for promoting tissue growth|
|US6511412||16 Oct 2000||28 Jan 2003||L. Vad Technology, Inc.||Cardivascular support control system|
|US6536260 *||11 Jul 2001||25 Mar 2003||Datascope Investment Corp.||Balloon catheter leak detection method and apparatus|
|US6553241||30 Aug 2001||22 Apr 2003||Mallinckrodt Inc.||Oximeter sensor with digital memory encoding sensor expiration data|
|US6591123||30 Aug 2001||8 Jul 2003||Mallinckrodt Inc.||Oximeter sensor with digital memory recording sensor data|
|US6606510||30 Aug 2001||12 Aug 2003||Mallinckrodt Inc.||Oximeter sensor with digital memory encoding patient data|
|US6622034||8 Sep 2000||16 Sep 2003||Imagenix, Inc.||Oximeter sensor with functional liner|
|US6628975||30 Aug 2001||30 Sep 2003||Mallinckrodt Inc.||Oximeter sensor with digital memory storing data|
|US6640138||4 Aug 2000||28 Oct 2003||Thermatrx, Inc.||Apparatus and method for heat treatment of tissue|
|US6679829||7 May 2001||20 Jan 2004||Paul Nigroni||Intra-aortic balloon pump having improved automated electrocardiogram based intra-aortic balloon deflation timing|
|US6735532||18 Nov 2002||11 May 2004||L. Vad Technology, Inc.||Cardiovascular support control system|
|US7074176 *||13 May 2004||11 Jul 2006||Innovamedica S.A. De C.V.||Air-pressure powered driver for pneumatic ventricular assist devices|
|US7085597||16 May 2003||1 Aug 2006||Mallinckrodt, Inc.||Oximeter sensor with digital memory recording sensor data|
|US7089064||30 Aug 2002||8 Aug 2006||Ams Research Corporation||Therapeutic prostatic thermotherapy|
|US7093601||2 Apr 2003||22 Aug 2006||Ams Research Corporation||Therapeutic prostatic thermotherapy|
|US7254946||12 Apr 1995||14 Aug 2007||Edwards Lifesciences Corporation||Thermodilution catheter having a safe, flexible heating element|
|US7468050||24 Dec 2003||23 Dec 2008||L. Vad Technology, Inc.||Long term ambulatory intra-aortic balloon pump|
|US7764983||1 Jun 2006||27 Jul 2010||Mallinckrodt Inc.||Method and circuit for storing and providing historical physiological data|
|US7809419||1 Jun 2006||5 Oct 2010||Mallinckrodt Inc.||Oximeter sensor with digital memory encoding sensor data|
|US7841985||22 Dec 2006||30 Nov 2010||Datex-Ohmeda, Inc.||Sensor identification method and system|
|US7857768||10 Oct 2008||28 Dec 2010||Starr Life Sciences Corporation||Integrated tail mounted blood pressure monitor and pulse oximeter system for animal research|
|US7881761||1 Jun 2006||1 Feb 2011||Mallinckrodt Inc.||Method and circuit for storing and providing historical physiological data|
|US7904131||1 Jun 2006||8 Mar 2011||Mallinckrodt Inc.||Method and circuit for storing and providing historical physiological data|
|US7949380||1 Jun 2006||24 May 2011||Mallinckrodt Inc.||Oximeter sensor with digital memory encoding sensor data|
|US7957781||2 Jun 2006||7 Jun 2011||Mallinckrodt Inc.||Method and circuit for storing and providing historical physiological data|
|US7976452 *||20 May 2008||12 Jul 2011||L.Vad Technology, Inc.||Long term ambulatory intro-aortic balloon pump with percutaneous access device|
|US7983729||1 Jun 2006||19 Jul 2011||Mallinckrodt Inc.||Method and circuit for storing and providing historical physiological data|
|US8000760||1 Jun 2006||16 Aug 2011||Mallinckrodt Inc.||Method and circuit for storing and providing historical physiological data|
|US8005624||26 Apr 2005||23 Aug 2011||Starr Life Sciences Corp.||Medical devices and techniques for rodent and small mammalian based research|
|US8010173||1 Jun 2006||30 Aug 2011||Mallinckrodt Inc.||Method and circuit for storing and providing historical physiological data|
|US8060170||1 Jun 2006||15 Nov 2011||Tyco Healthcare Group||Method and circuit for storing and providing historical physiological data|
|US8064974||1 Jun 2006||22 Nov 2011||Tyco Healthcare Group Lp||Method and circuit for storing and providing historical physiological data|
|US8068889||1 Jun 2006||29 Nov 2011||Tyco Healthcare Group Ip||Oximeter sensor with digital memory encoding sensor data|
|US8078247||2 Jun 2006||13 Dec 2011||Tyco Healthcare Group Lp||Method and circuit for storing and providing historical physiological data|
|US8090425||30 Sep 2005||3 Jan 2012||Tyco Healthcare Group Lp||Oximeter sensor with digital memory encoding patient data|
|US8095195||2 Jun 2006||10 Jan 2012||Tyco Healthcare Group Lp||Method and circuit for storing and providing historical physiological data|
|US8096942 *||10 Oct 2006||17 Jan 2012||Olympus Corporation||Endoscope balloon control device|
|US8103325||1 Jun 2006||24 Jan 2012||Tyco Healthcare Group Lp||Method and circuit for storing and providing historical physiological data|
|US8112136||1 Jun 2006||7 Feb 2012||Tyco Healthcare Group Lp||Method and circuit for storing and providing historical physiological data|
|US8112137||2 Jun 2006||7 Feb 2012||Tyco Healthcare Group Lp||Method and circuit for storing and providing historical physiological data|
|US8185178||30 Sep 2005||22 May 2012||Tyco Healthcare Group Lp||Oximeter sensor with digital memory encoding patient data|
|US8298154||10 Jan 2008||30 Oct 2012||Starr Life Sciences Corporation||Techniques for accurately deriving physiologic parameters of a subject from photoplethysmographic measurements|
|US8323174||18 Nov 2011||4 Dec 2012||Nupulse, Inc.||Skin interface for ventricular assist device|
|US8326421||21 Feb 2012||4 Dec 2012||Nupulse, Inc.||Ventricular assist device|
|US8439825 *||3 Nov 2005||14 May 2013||Fujifilm Corporation||Balloon controller for endoscopic apparatus|
|US8540618||2 Feb 2004||24 Sep 2013||L-Vad Technology, Inc.||Stable aortic blood pump implant|
|US8540667 *||8 Mar 2011||24 Sep 2013||Sanovas, Inc.||Multi-balloon catheter for extravasated drug delivery|
|US8597239 *||1 Mar 2011||3 Dec 2013||Sanovas, Inc.||Abrading balloon catheter for extravasated drug delivery|
|US8608637 *||12 Jan 2012||17 Dec 2013||Nupulse, Inc.||Internal drive line for ventricular assist device|
|US8626256||1 Jun 2006||7 Jan 2014||Covidien Lp||Oximeter sensor with digital memory encoding sensor data|
|US8639307||1 Jun 2006||28 Jan 2014||Covidien Lp||Oximeter sensor with digital memory encoding sensor data|
|US8684905 *||21 Feb 2012||1 Apr 2014||Nupulse, Inc.||Intra-aortic balloon pump assembly for ventricular assist device|
|US8696621||13 Jul 2012||15 Apr 2014||Sanovas, Inc.||Resector balloon system|
|US8790299||13 Jul 2012||29 Jul 2014||Sanovas, Inc.||Balloon resection method|
|US8905029 *||1 Sep 2009||9 Dec 2014||Covidien Lp||Airway system with carbon dioxide sensor for determining tracheal cuff inflation and technique for using the same|
|US20040152945 *||2 Feb 2004||5 Aug 2004||Adrian Kantrowitz||Stable aortic blood pump implant|
|US20040167589 *||22 Feb 2003||26 Aug 2004||Chester Heath||Viral-inhibiting apparatus and methods|
|US20040193023 *||28 Mar 2003||30 Sep 2004||Aris Mardirossian||System, method and apparatus for monitoring recording and reporting physiological data|
|US20040230089 *||13 May 2004||18 Nov 2004||Emilio Sacristan||Air-pressure powered driver for pneumatic ventricular assist devices|
|US20060025660 *||30 Sep 2005||2 Feb 2006||David Swedlow||Oximeter sensor with digital memory encoding patient data|
|US20060030762 *||30 Sep 2005||9 Feb 2006||Swedlow David||Oximeter sensor with digital memory encoding patient data|
|US20060030765 *||30 Sep 2005||9 Feb 2006||David Swedlow||Oximeter sensor with digital memory encoding patient data|
|US20060095063 *||3 Nov 2005||4 May 2006||Fujinon Corporation||Balloon controller for endoscopic apparatus|
|US20060217604 *||1 Jun 2006||28 Sep 2006||Nellcor Puritan Bennett Inc.||Oximeter sensor with digital memory encoding sensor data|
|US20060217605 *||1 Jun 2006||28 Sep 2006||Nellcor Puritan Bennett Inc.||Oximeter sensor with digital memory encoding sensor data|
|US20060217606 *||1 Jun 2006||28 Sep 2006||Nellcor Puritan Bennett Inc.||Oximeter sensor with digital memory encoding sensor data|
|US20060217607 *||1 Jun 2006||28 Sep 2006||Nellcor Puritan Bennett Inc.||Oximeter sensor with digital memory recording sensor data|
|US20060217608 *||1 Jun 2006||28 Sep 2006||Nellcor Puritan Bennett Inc.||Oximeter sensor with digital memory encoding sensor data|
|US20060224059 *||1 Jun 2006||5 Oct 2006||Nellcor Puritan Bennett Inc.||Method and circuit for storing and providing historical physiological data|
|US20060229511 *||1 Jun 2006||12 Oct 2006||Nellcor Puritan Bennett Inc.||Oximeter sensor with digital memory recording sensor data|
|US20070049810 *||1 Jun 2006||1 Mar 2007||Nellcor Puritan Bennett Inc.||Method and circuit for storing and providing historical physiological data|
|US20070055101 *||10 Oct 2006||8 Mar 2007||Olympus Corporation||Endoscope balloon control device|
|US20070073372 *||8 Nov 2006||29 Mar 2007||Chester Heath||Viral-inhibiting apparatus and methods|
|US20070088207 *||2 Jun 2006||19 Apr 2007||Nellcor Puritan Bennett Inc.||Method and circuit for storing and providing historical physiological data|
|US20100078030 *||1 Sep 2009||1 Apr 2010||Nellcor Puritan Bennett Llc||Airway system with carbon dioxide sensor for determining tracheal cuff inflation and technique for using the same|
|US20110152683 *||23 Jun 2011||Gerrans Lawrence J||Abrading Balloon Catheter for Extravasated Drug Delivery|
|US20110218494 *||8 Sep 2011||Gerrans Lawrence J||Multi-Balloon Catheter for Extravasated Drug Delivery|
|US20120108886 *||3 May 2012||Nupulse, Inc.||Internal drive line for ventricular assist device|
|US20120149970 *||21 Feb 2012||14 Jun 2012||Nupulse, Inc.||Intra-aortic balloon pump assembly for ventricular assist device|
|US20140024903 *||20 Sep 2013||23 Jan 2014||Lawrence J. Gerrans||Abrading Balloon Catheter for Extravasated Drug Delivery|
|WO1989011890A1 *||2 Jun 1989||14 Dec 1989||Advanced Surgical Intervention||Balloon dilation catheter|
|WO1995000187A1 *||16 May 1994||5 Jan 1995||Datascope Investment Corp||Noise-attenuating pneumatic compressor|
|WO1995000198A1 *||24 Jun 1994||5 Jan 1995||Boston Scient Corp||Dilation catheter and method of treatment therewith|
|U.S. Classification||600/18, 604/118, 604/914|
|International Classification||F04B45/00, A61M1/10, A61B1/00, F04B45/033|
|Cooperative Classification||A61M1/1072, A61M2205/6018, F04B45/033, A61B1/00112, A61M2205/6027, A61M1/106|
|European Classification||A61B1/00F, F04B45/033, A61M1/10E4H|
|3 Nov 1982||AS||Assignment|
Owner name: KONTROL CARDIOVASCULAR INC., EVERETT, MA A CORP. O
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST.;ASSIGNOR:AVCO CORPORATION, A CORP. OF DE;REEL/FRAME:004061/0445
Effective date: 19820928