the present invention provides an ultrasound imaging system suitable for measuring cardiac output of a patient &# 39 ; s heart , said system comprising : ( 1 ) an ultrasound imaging catheter comprising at least one transducer utilizing piezoelectric properties to generate acoustic signals from electrical signals in order to obtain ultrasound signals , wherein the at least one transducer is suitable for insertion into the patient &# 39 ; s heart and to obtain ultrasound signals associated with an area of the patent &# 39 ; s heart in which cardiac output is to be measured ; ( 2 ) digital and / or analog electronics capable of generating and processing ultrasound signals from the at least one transducer to generate b - mode , m - mode , or doppler representations of the cardiac output of the patient &# 39 ; s heart ; and ( 3 ) an associated computer that can generate and process the ultrasound signals in order to measure the cardiac output in the patient &# 39 ; s heart . this invention also provides a method of placing an electrode at a desired position at or near the left ventricle of a patient &# 39 ; s heart in order to electrically activate the left ventricle of the patient &# 39 ; s heart using the electrode , said method comprising : ( 2 ) placing an ultrasound imaging catheter in a position to image the left ventricle of the patient &# 39 ; s heart , wherein the ultrasound imaging catheter comprises at least one transducer utilizing piezoelectric properties to generate acoustic signals from electrical signals in order to obtain ultrasound signals and wherein the at least one transducer is suitable for insertion into the patient &# 39 ; s heart and to obtain ultrasound signals associated with an area of the patent &# 39 ; s heart ; ( 3 ) utilizing the ultrasound imaging catheter to image the electrode at or near the left ventricle of a patient &# 39 ; s heart and to guide the electrode to the desired position ; and ( 4 ) attaching the electrode to the desired position . one preferred desired position for attachment of the electrode is the upper portion of the left ventricle ( i . e ., nearer the base of the heart as compared to the apex ). in one preferred embodiment , at least one transducer has a defecting or rotation element whereby the transducer , once positioned to image the left ventricle of the patient &# 39 ; s heart , can be easily rotated or moved in order to image other portions of the patient &# 39 ; s heart . the present invention also provides an ultrasound imaging system to assist in cardiac electrophysiology procedures related to a patient &# 39 ; s heart , said system comprising : ( 1 ) an ultrasound imaging catheter comprising a multi - element array transducer utilizing piezoelectric properties to generate acoustic signals from electrical signals in order to obtain ultrasound signals , wherein the multi - element array transducer is suitable for insertion into the patient &# 39 ; s heart and to obtain ultrasound signals associated with the patent &# 39 ; s heart ; ( 2 ) digital and / or analog electronics capable of generating and processing ultrasound signals from the multi - element array transducer to generate and display a representation of ( a ) the electrocardiogram of the patient &# 39 ; s heart , ( b ) a real time image of the patient &# 39 ; s heart , or ( c ) the cardiac output of the patient &# 39 ; s heart . in a preferred embodiment , the representation ultrasound signals can be displayed relative to , and compared to , a voltage conduction map of the patient &# 39 ; s heart ( i . e ., a representation of the progression of electrical activation / deactivation or “ action potentials ” of the muscles of the heart ). the basis of the measurement / estimation process of the present invention is shown in fig6 and 7 . using the doppler process ( fig6 ), the amplitude of the velocity profile is halved to provide the average velocity across the flow area ( fig6 a ). the velocity is integrated ( fig6 b ) with respect to time from the start of the pulse ( t0 ) to the end of the pulse ( t1 ). such integration can also include the negative peaks shown in fig4 a to compensate for reverse flows . the result of this integration with respect to time is then multiplied by the cross - sectional area of the flow to provide the ejection volume ( fig6 c ). the integration length can also be set by integrating during the complete cardiac cycle ( i . e ., through one complete cycle of the ecg ). the spectrum in fig6 can also be obtained by either frequency and / or amplitude plotting of an audio signal . v ejt = a   ∫ v peak 2   t eq .  1 using the m - mode process ( fig7 ), the system outputs the relative position of the two walls of the ventricle as a function of time . the ventricle can be equated to an ellipsoid shape , whose secondary radius is represented by the distance between the two walls measured by the m - mode . the primary equation to the volume would then be v =( π ( r 1 + c 1 ) r 2 )( 2 πr 2 )± c 2 eq . 2 c 1 = a correction factor to compensate for the difference in morphology of the ventricle w . r . t . an ellipse ; and c 2 = correction in the primary radius to compensate for longitudinal contractility of the ventricle during a cardiac cycle . volume can then be calculated at systole and diastole ( determined either with correlation to the ecg , as shown in fig7 or by determining the minimum and maximum of the m - mode curve ). the stroke volume is then given by one embodiment of the present invention is in the form of hardware and / or software that exists as part of the ultrasound scanner ( fig1 ). in such an embodiment , the system utilizes the doppler processing capabilities of the host ultrasound scanner to obtain a time - varying signal representative of the velocity of flow through an area of interest . such area could include the inlet of the aorta from the left ventricle , or the valve in between . the system also utilizes a view / measure of the cross - sectional area through which the flow of interest is to pass ( fig5 ). the doppler system outputs the spectral information , which is indicative of the velocity of flow through the volume of interest ( as shown in fig3 ) either by means of showing a spectrum ( which in some embodiments can be obtained in a analog or digital format from the machine ). such a spectrum can be obtained either by obtaining a longitudinal sectional view of the flow axis at any angle ( as represented in fig3 ), or by obtaining a cross sectional view of the flow conduit ( fig5 ). such calculations of flow / area can be compensated for the angle of measurement using a cosine of the angle w . r . t . actual plane correction . for conditions where the flow is perpendicular to the sample volume of the doppler system , other estimation techniques such as “ transverse doppler ,” which utilizes the doppler bandwidth to assess flow at flow to beam angles close to 90 degrees , can be utilized . tortoli et al ., ultrasound med . biol ., 21 , 527 - 532 ( 1995 ). this doppler signal can also be as an audio signal ( again , either in analog or digital format ) as a frequency and / or amplitude modulated signal that is indicative of the spectrum and hence the flow velocity through the area of interest . this could further include ecg signals ( again , in analog or digital format ). further processing can be carried out , for example , using the following techniques : 1 . a largely manual process wherein the user measures / demarcates , either with or without the aid of an ecg , the peak velocities at least one point on the spectrum and demarcates / measures the cross - section of the outlet of the ventricle ; and the system / calculating tool ( either on the ultrasound machine or on a separate computer ) the integrates the curve over time to obtain stroke volume via equation 1 . 2 . a semi - automated process wherein the system ( either on the ultrasound machine or separate ) automatically integrates the curve with or without the help of an ecg while the user inputs the area of interest of the orifice through which the flow passes . 3 . a fully automated process wherein the system prompts the user to obtain particular views of the anatomy of interest and demarcate specific points and the system then processes the data as above with , however , the system internally tracking the data of interest . 4 . the system automatically integrates the curve from beat to beat , and outputs the stroke volume in any sort of display , having obtained the cross sectional area using the techniques mentioned in point 2 or 3 above . of course , various combinations and / or modifications of these techniques can be used if desired and depending on the particular application and / or patient . another embodiment of the present invention is in the form of hardware and / or software that exists separate from the ultrasound scanner console or workstation with means to communicate either video and / or audio and / or other signals between the ultrasound scanner and / or the display computer / system . communication between such workstation and the ultrasound scanner could include video , audio , and / or any ecg signals in digital and / or analog format . the above described processing can then be performed either partially or entirely on the workstation . in another embodiment of the present invention , the m - mode output is utilized to measure stroke volume . again , this system can comprise of hardware and / or software that resides wholly on the ultrasound scanner or can also include hardware and / or software on a separate workstation with means to communicate either digital and / or analog data with the ultrasound scanner ( fig1 and 2 ). the volume can then be estimated , as given earlier by equations 2 and 3 ( fig7 ). processing can be carried out , for example , using the following techniques : 1 . a largely manual process wherein the user measures / demarcates , either with or without the aid of an ecg , the systolic and diastolic distances between the two ventricular walls , and the system / calculating tool ( either on the ultrasound machine or on a separate computer ) calculates the stroke volume . this process can include , if desired , provisions for the user or system to record / obtain the correction factors described in equation 2 . 2 . a semi - automated process wherein the system ( either on the ultrasound machine or separate ) automatically measures the distances and estimates the stroke volume with or without the help of an ecg . in this case , the system can automatically measure / estimate the correction factors described in equation 2 , or the user can specify or aid the system in estimating / measuring these factors . 3 . a fully automated process wherein the system prompts the user to obtain particular views of the anatomy of interest and demarcate specific points and the system then processes the data as above with , however , the system internally tracking the data of interest . 4 . the system automatically measures the stroke volume , with data obtained from any of the above described methods , and outputs the stroke volume in any sort of display , having obtained the cross sectional area using the techniques mentioned in points 2 or 3 above . a yet another embodiment can include hardware and / or software separate from the ultrasound scanner , in the form of a workstation wherein there exists a mode of communication , either analog or digital , between the workstation and the ultrasound scanner or catheter . cabling from the ultrasound machine to the catheter ( especially with a multi element array catheter ) and from the catheter proximal connector to the catheter transducer housed at the distal tip can be expensive . to reduce cost , the ultrasound machine could be moved adjacent to the patient , thereby allowing a relatively short cable to be used to attach the catheter . in some cases , however , this may be impractical since most catheter rooms are sterile or semi - sterile environments and , thus , the ultrasound machine may be some distance from the patient &# 39 ; s bedside . thus , a connecting cable which is reusable ( and probable non - sterile ) is desirable , as opposed to the catheter itself , which is sterile and usually not re - usable . it would be desirable if this connecting cable could be used as a universal cable in that it could be used with many ultrasound machines . while many ultrasound machines have a standard 200 pin zip connector , most ultrasound machines do not have patient isolation means built in to the degree necessary for percutaneous catheter use . therefore , in another embodiment , the system of this invention employs a connector cable with an isolation means or isolation box that is external to the ultrasound machine itself . preferably the isolation box , which houses a plurality of isolation transformers , is relatively small so that it could be placed easily on or near the patient &# 39 ; s bed . such a cable could easily accommodate all operational communication between the catheter and the ultrasound machine and / or the appropriate computer workstation . in still another embodiment , the ultrasonic catheter further comprises a temperature sensing and / or control system . especially when used at higher power ( e . g ., when using color doppler imaging ) and / or for lengthy periods of time , it is possible that the transducer , and hence , the catheter tip , generate heat that may damage tissue . while computer software can be used to regulate the amount of power put into the catheter to keep the temperature within acceptable ranges , it is also desirable to provide a temperature sensing means as well as a safety warning and / or cut - off mechanism for an additional margin of safety . actual temperature monitoring of the catheter tip is most desirable , with feedback to the computer , with an automatic warning or shut down based upon some predetermined upper temperature limit . the system could be programed to provide a warning as the temperature increases ( e . g ., reaches 40 ° c . or higher ) and then shut off power at some upper limit ( e . g ., 43 ° c . as set out in u . s . fda safety guidelines ). to monitor the temperature at or near the tip of the catheter ( i . e ., in the region of the ultrasound transducer ), a thermistor may be used . the temperature at the tip of the catheter could be continuously monitored via appropriate software . although the software could also provide the means to control the power to the catheter in the event that excessive temperatures are generated , it would also be desirable to have a back up shut off or trip mechanism ( e . g ., a mechanical shut off or tripping means ). of course , various combinations and / or modifications of these techniques and systems can be used if desired and depending on the particular application and / or patient . it is to be understood , however , that even though numerous characteristics and advantages of the present invention have been set forth in the foregoing description , along with details of the structure and function of the invention , the disclosure is only for illustrative purposes . changes may be made in detail , especially in matters of shape , size , arrangement , and storage / communication formats within the principles of the invention to the full extent indicated by the broad general meaning of the terms in which the appended claims are expressed .
a method and system for estimating the volume of blood ejected from the left ventricle of the heart to a succeeding chamber / conduit , or vice - versa , while imaging the intersection of such structures is described . the process utilizes either the m - mode to estimate volume differences in a view of the ventricle over time or doppler processing techniques to obtain flow profiles across intersections , or blood vessels , which are then utilized to calculate output . this process can be combined with ecg guidance / triggering to measure / track changes in output from beat to beat , or during the course of an evaluation or therapeutic procedure . this process can be specifically used for the placement of permanent pacemaker electrodes .