Title of Invention

PATIENT MONITORING SYSTEM WITH PORTABLE MONITOR FOR MEASURING BODY CARDIAC OUTPUT USING IMPEDANCE PLYTHESMOGRAPHY

Abstract The present invention provides a noninvasive and portable medical monitoring system for monitoring the change in time of the electrical impedance of a portion of a living body, such as the lungs or the brain with an inbuilt data acquisition system and a PC motherboard. The present invention also provides a computer implementable method for monitoring and measurement of cardiac output and blood flow index using impedance plythesmographic techniques.
Full Text PATIENT MONITORING SYSTEM WITH PORTABLE MONITOR FOR MEASURING BODY CARDIAC OUTPUT USING IMPEDANCE
PLYTHESMOGRAPHY
A) Field of the invention
1. The present invention relates to noninvasive medical monitoring systems and,
more particularly, to a method and device for monitoring the change in time of the
electrical impedance of a portion of a living body, such as the lungs or the brain.
More particularly, the present invention relates to a portable monitoring system for
measurement of cardiac output and blood flow index using impedance
plythesmographic techniques.
B) Background of the invention
2. The accurate monitoring and measurement of cardiac output has long been a
clinical and research goal. Several methods are known for the monitoring and
measurement of cardiac output including both direct and indirect methods. The
measurement and monitoring of cardiac output has been known for over seventy
years. A representative and not an exhaustive list are given below in respect of the
various methods employed for measurement and monitoring of cardiac output.
3. Direct methods for measurement and monitoring of cardiac output are generally
more accurate but are largely restricted to research laboratories due to the invasive
or traumatic procedures, which need to be employed. Indirect methods such as the
steady-state Fick oxygen uptake, the transient indicator dilution method, and
anemometry are less invasive but are not very accurate.

4. Of the less invasive indirect methods, the transient indicator dilution procedure
using iced liquids injected through the lumen of a Swan-Ganz catheter is currently
the most frequently employed clinical method. This method requires the least
amount of specialized equipment is portable to the patent's bedside and can be
repeated often. However, the transient indicator dilution procedure requires a
specially trained physician to thread an expensive catheter through the right side of
the heart and into the pulmonary artery. During long term monitoring, infection at
the site of catheter insertion and damage to the blood vessels of the lung are
constant hazards. The Swan-Ganz catheters may also need to be repositioned or
replaced after a few days of use. Accuracy and repeatability of the thermal dilution
Swan-Ganz method are typically only about 10%, even under precisely controlled
laboratory conditions.
5. Non-invasive indirect methods also includes the ballistocardiography method
which requires a patient to lie motionless on a large inertial platform, the soluble
gas uptake method which requires a patient to sit in a small chamber for many
minutes and the impedance plethysmography method which measures small
changes in electrical impedance on the surface of the chest. The first two non-
invasive methods are not readily utilized because the special equipment needed is
extremely large and inconvenient to use. In impedance plethysmography, accuracy
is difficult to obtain and is thus not normally preferred.
6. Representative heart imaging techniques include 2-D cine-angiography and 2D
echo-cardiography wherein a series of x-ray or ultrasound images of the beating
heart are measured to determine left ventricle systolic and diastolic volumes, 3-D
ECG-gated MRI and radioactive imaging methods where many images of the
heart are made during particular phases of the cardiac cycle can also be employed.
These methods require large, expensive equipment, and measurements are time


consuming and require the efforts of several highly trained specialists to obtain and interpret results.
7. A significant problem associated with heart diseases is the fluid buildup such as
acute edema of the lungs. Since these fluids are electrically conductive, changes in
their volume can be detected by the technique of impedance plethysmography, in
which the electrical impedance of a part of the body is measured by imposing an
electrical current across the body and measuring the associated voltage difference.
For example, experiments with dogs (R. V. Luepker et al., American Heart Journal,
Vol. 85, No. 1, pp 83-93, January 1973) have shown a clear relationship between
the transthoracic electrical impedance and the change in pulmonary fluid volume.
8. Several methods are known in the art for monitoring of pulmonary edema using
two electrodes, one either side of the biological object. However, such methods
have proved to be unfit for prolonged monitoring due to the drift of skin-to-
electrode contact layer resistance. This drift is due to ions from sweat and skin
penetrating the electrolytic paste of the electrode, and the wetting of the epidermis,
over the course of several hours. A method for overcoming this problem was
developed by Kubicek et al. (Annals of the New York Academy of Sciences, 1970,
170(2):724-32; U.S. Pat. No. 3,340,867, reissued as Re. Pat. No. 30,101). Related
U.S. patents include Asrican (U.S. Pat. No. 3,874,368), Smith (U.S. Pat. No.
3,971,365), Matsuo (U.S. Pat. No. 4,116,231) and Itoh (U.S. Pat No. 4,269,195).
The method of Kubicek et al. uses a tetrapolar electrode system whereby the outer
electrodes establish a current field through the chest. The inner voltage pickup
electrodes are placed as accurately as is clinically possible at the base of the neck
and at the level of the diaphragm. This method regards the entire portion of the
chest between the electrodes as a solid cylinder with uniform parallel current fields
passing through it. However, because this system measures the impedance of the
entire chest, and because a large part of the electrical field is concentrated in the

surface tissues, this method is not sufficiently specific for measuring liquid levels in the lungs and has low sensitivity: 50 ml per Kg of body weight (Y. R. Berman, W. L. Schutz, Archives of Surgery, 1971.V.102-.61-64). It should be noted that such sensitivity has proved to be insufficient for obtaining a significant difference between impedance values in patients without pulmonary edema to those with an edema of average severity (A. Fein et al., Circulation, 1979, 60(5):l 156-60). In their report on the conference in 1979 concerning measuring the change in the liquid level in the lungs (Critical Care Medicine, 1980,8(12):752-9), N. C. Staub and J. C Hogg summarize the discussion on the reports concerning the reports on the method of Kubicek et al. for measuring thoracic bio-impedance. They conclude that the boundaries of the normal values are too wide, and the sensitivity of the method is lower than the possibilities of clinical observation and radiological analysis, even when the edema is considered to be severe. It is indicative that, in a paper six years later by N. C. Staub (Chest. 1986,90(4):588-94), this method is not mentioned at all. Other problems with this method include the burdensome nature of the two electrodes tightly attached to the neck, and the influence of motion artifacts on the impedance readings received.
'. Another method for measuring liquid volume in the lungs is the focusing electrode bridge method of Severinghaus (U.S. Pat. No. 3,750,649). This method uses two electrodes located either side of the thorax, on the left and right axillary regions. Severinghaus believed that part of the electrical field was concentrated in surface tissues around the thorax and therefore designed special electrodes to focus the field through the thorax. This method does not solve the problems associated with the drift in the skin-to-electrode resistance described above. An additional problem is the cumbersome nature of the large electrodes required. It is indicative that the article by Staub and Hogg, describing the 1979 conference, mentions that the focusing bridge transthoracic electrical impedance device was not discussed, despite the presence of its developer at the conference. A review by M. Miniati et
/2-

al. (Critical Care Medicine, 1987,15(12):1146-54) characterizes both the method of Kubicek et al. and the method of Severinghaus as "insufficiently sensitive, accurate, and reproducible to be used successfully in the clinical setting" (p. 1146).
10. Toole et al., in U.S. Pat. No. 3,851,641, addresses the issue of electrode drift by
measuring the impedance at two different frequencies. However, their method is
based on a simplified equivalent circuit for the body in which the resistances and
capacitances are assumed to be independent of frequency. Pacela, in U.S. Pat No.
3,871,359, implicitly addresses the issue of electrode drift by measuring two
impedances across two presumably equivalent parts of a body, for example, a right
and a left arm or a right and a left leg, and monitoring the ratio between the two
impedances. His method is not suitable for the monitoring of organs such as the
lungs, which are not symmetric, or the brain, of which the body has only one.
Other notable recent work in measuring the impedance of a portion of the body
includes the tomographic methods and apparatuses of Bai et al. (U.S. Pat. No.
4,486,835) and Zadehkoochak et al. (U.S. Pat. No. 5,465,730). In the form
described, however, tomographic methods are based on relatively instantaneous
measurements, and therefore are not affected by electrode drift. If tomographic
methods were to be used for long-term monitoring of pulmonary edema, they
would be as subject to electrode drift problems as the other prior art methods.
11. As seen above, it is important to estimate cardiac output Noninvasive estimates of
cardiac output (CO) can be obtained using impedance cardiography. Strictly
speaking, impedance cardiography, also known as thoracic bio-impedance or
impedance plethysmography, is used to measure the stroke volume of the heart.
Cardiac output is obtained when the stroke volume is multiplied by heart rate.
12. Heart rate is obtained from an electrocardiogram. The basic method of correlating
thoracic, or chest cavity, impedance, ZT (t), with stroke volume was developed by
13

Kubicek, et al. at the University of Minnesota for use by NASA. See, e.g., U.S. Reissue Patent No. 30,101 entitled "Impedance plethysmograph" issued Sep. 25, 1979, which is incorporated herein by reference in its entirety. The method generally comprises modeling the thoracic impedance ZT (t) as a constant impedance, Zo, and time-varying impedance, 8Z (t). The time-varying impedance is measured by way of an impedance waveform derived from electrodes placed on various locations of the subject's thorax; changes in the impedance over time can then be related to the change in fluidic volume (i.e., stroke volume), and ultimately cardiac output.
13. In order to do the cardiac output measurement selection of'a','b'5 fc' and 'x' points
is necessary on the time varying impedance graph. The 'c' point being the peak
point, 'a' and 'x' points can be identified as the lowest points on the left and the
right side of point 'c' respectively. V point can located in between 'a'and V points
at the start of the peak. But it can be tricky to identify these points manually and
human error in judgement could mean error in diagnosing the exact condition of
the patient. Hence it is important to develop better ways of identifying these
points so that more accurate measurement of cardiac output can happen.
14. Also the existing apparatus for non-invasive cardiac output measurement are not
easy to use and involve complex connections. They typically involve a
conventional stand alone PC connected to plethysmography related gadgets.
Which means, the equipment as a whole is cumbersome to use and cannot be
moved around easily to take the equipment near a patient if required.
15. The existing apparatus are also limited in their capacity to do analysis based on a
particular patient's data due to limitations in the software being employed as part
of the apparatus.

16. Based on the foregoing, there is a need for an improved apparatus and method for
measuring cardiac output in a living subject. Such improved apparatus and method
ideally be easy to use and operate, would allow the clinician to repeatedly and
consistendy identify the 'a', 'b', 'c' and 'x' points for accurate measurement of
cardiac output and also allow repeated analysis on a patient's data for assisting the
clinician in diagnosing the situation in the most accurate manner.
C) Objects of the invention
17. One object of the invention is to provide an integrated and easy to use impedance
plethysmograph apparatus.
18. Another object of the invention is to provide accurate measurement of cardiac
output by providing both intermittent and continuous cardiac output
measurement modes, wherein under the continuous output measurement mode,
the selection of points on the time varying impedance graph happens automatically
and under the intermittent mode, the selection of points needs to be done
manually.
19. Another object of the present invention is to extract respiration rate waveform,
which is another important parameter to be monitored that gives an indication of
the stress condition of the patient.
20. Another object of the present invention is to provide facility to re-analyze a
patient's data after doing a first analysis by storing the patients data in the storage
memory with a unique identifier for the patient enabling easy retrieval for re-
analysis.
is

21. Another object of the present invention is to provide low cost solution to the
existing impedance plethysmograph apparatus by providing digital solutions to
existing analog circuitry.
22. Another object of the present invention is to provide an apparatus that can be
used both for non-invasive cardiac output monitoring and vascular measurement
monitoring.
D) Summary of the invention
23. Accordingly, the present invention provides a noninvasive and portable medical
monitoring system for monitoring the change in time of the electrical impedance
of a portion of a living body, such as the lungs or the brain. The present invention
also provides a method for monitoring and measurement of cardiac output and
blood flow index using impedance plythesmographic techniques. The present
invention uses a tetra polar electrode method with a TFT display unit to measure,
in litres, the blood pumped by the heart at a given period of time with an option to
trace vascular resistance. The present invention measures the change in the body
surface impedance due to pulsetile blood flow by injecting carrier charges such as a
low amplitude sinusoidal current with a high frequency such as 48 kHz and
monitoring the voltage variations along the current path.
24. The present invention also provides facility store copies of patient information and
waveforms with an unique identifier for easy retrieval and re-analysis. The
invention also reduces the complex analog circuitry found in the conventional
plethysmograph apparatus by using digital solutions for the same circuitry,
especially in the circuitry for cal pulse generation and carrier sine wave generation.
16

E) Brief description of the accompanying drawings
25. Figure 1 provides a schematic block diagram of the system of the invention.
26. Figure 2 shows the block diagram of an exemplary analog system for cal pulse
generation and carrier sine wave generation.
27. Figure 3 shows a preferred embodiment of the digital implementation of the cal
pulse generation and carrier sine wave generation of the present invention.
28. Figure 4 shows the block diagram of an exemplary analog circuitry for generating
dZ/dt differentiated waveform.
29. Figure 5 shows a preferred embodiment of the digital implementation of the
circuitry for generation of dZ/dt differentiated waveform.
30. Figure 6 is a representative rate of change of impedance waveform.
7) Detailed description of the invention
31. The present invention relates to a medical monitoring system and more
particularly to a method and portable device for monitoring volume of fluid
associated with the heart. In other words, the invention is used to measure the
volume of blood pumped by the heart per minute, namely the blood flow index.
As these fluids are electrically conductive, charges in their volumes can be detected
by the technique of impedance plythesmography wherein the electrical impedance
of a part of the body is measured by imposing an electrical current across the body
and measuring the associated voltage difference.
11

32. The system of the invention provides an apparatus for monitoring cardiac output
using impedance plythesmographic techniques and tracing vascular resistance
using a dedicated menu option. Thus different options are provided for working
of the monitor. The method uses tetrapolar electrode systems. One pair of
electrodes is utilised for sensing voltage drop along the current path that takes
place due to changing blood flow with heart beat. The monitor of the invention is
particularly advantageous since it is portable. In addition multiple keys are
provided along with an optical encoder for data entry and menus selection. The
display monitor can be a 10.4 inch TFT display panel and is provided with a back
up power source.
33. The method of the invention comprises of:
a. Signal acquisition and signal conditioning.
b. Computation of cardiac output, blood flow index using the tetra polar
electrode method;
c. Display of the results of the signal acquisition and conditioning, computation
of the cardiac output and the blood flow index on a 10.4" TFT monitor.
34. Figure 1 shows the system block diagram. The external ac voltage (works from 95-
265V 60H2/50 Hz) (230 V) has to be converted into a DC (12-13.8V) voltage
initially as shown in the block diagram, which is fed to the DC-DC converter card
and parrellely to Single Board computer DC-DC converter(SBC DC-DC). The
SBC DC-DC supplies Power to the single board computer. DC-DC Converter
supplies to the rest of the Boards like NICO Amp card (In block it is mentioned
as analog and digital + ISO ), Inverter card, Key board, Fan (to keep the temp
cooling inside), because all these boards need a constant DC voltage for its
operation. The SBC has a two way communication with the hard disk drive(HDD)
for storing data and retrieving information from the hard disk. The DC voltage is
19

again converted to ac voltage by the inverter for the display backlight unit as shown in the block diagram. NICO amp card is specially designed to provide 5 kV patient Isolation and less than 10 uA patient leakage current. The analog and digital PWA (Nico Amp card) are used to gather (Impedance changes) and ECG signals from the patient body, demodulate, signal condition by removingnoise, amplify it and then digitize and display as a waveform on the display.. The NICO Amp card also has the in built ECG generation circuit to facilitate the Nico calculation. Nico Amp card also has the on board CAL pulse generation to facilitate the user to check the calibration status of the unit without opening the it. This on board Cal Pulse gives facility to do on site calibration without any speciliased equipment to be carried for the same. There is a isolator to isolate the voltage in the ECG circuit to 5 kV. The Nico waveformis managed by a keyboard, which can keeps the waveform the following states:
• start/stop
• freeze/de-freeze
The On/off key of the key board is used to start and stop the key board.
35. The system is designed such that power supply to display invertor is given only
after sensing that SBC DC-DC has switched on, so that the display comes once
the SBC has booted to give good impression of the product. Also during switch
off if the on/off key is pressed for three seconds and then software senses and
shut down the software and then both the DC-DC converters will shut off. The
waveform from the PWA is fed back to the single board computer which then
displays it on the display unit.
36. Signal acquisition is carried out using an acquisition board. The computation is
carried out using a digital board which uses a Intel 80c251 processor and a mother
board. The unit has the facility to load NICO software without opening the unit

though USB port. The unit also has the Key board and mouse interface facility to type the letters in the menu and selection of the points on the waveform more accurately. The unit also has the VGA out put to connect to the external monitor as well as Project to connect bigger displays.
Circuitry for cal pulse generation and carrier sine wave generation
37. Figure 2 shows the block diagram of an exemplary analog system for cal pulse
generation and carrier sine wave generation. The sine wave current source (1) is
typically EPROM driven and contains sine wave values, and generates a 48 kHz
sine wave. The sine wave current generator passes the sine wave of constant
amplitude through the body segment in "patient mode" with the help of an
isolation X' mer and relay. The sine wave current generator also passes a modulated
sine wave current (1% amp. modulation with triangular wave of lHz frequency) to
the calibration n/w of fixed resistor values in the calibration mode. The voltage
signal developed in the Current' path is sensed with the help of sensing electrodes
and amplified using a differential amplifier. The high 'Q' band pass filter removes
the super imposed noise and the output of the filter is rectified by precision
rectifier and filtered to obtain a filtered (output) signal 'Z', that is proportional to
the instantaneous electrical impedance of the body segment, under investigation.
38. Figure 3 shows a preferred embodiment of the digital implementation of the cal
pulse generation and carrier sine wave generation of the present invention. A
single micro controller with DAC will replace the triangular wave generator,
amplifier & multiplexer and the microcontroller blocks shown in Figure 3. Also
the address generator and EPROM is replaced by using Numerically controlled
Oscillator (NCO). Thus circuit is made much simpler and cost effective along with
all the benefits of accuracy associated with digital circuits.
2o

Circuitry for generating dZ/dt differentiated wavcfotm
39. Figure 4 shows the block diagram of an exemplary analog circuitry for generating
dZ/dt differentiated waveform. This signal is attenuated and fed to ADC input of
the digital circuit comprising microcontroller Intel 80-c251. The initial value of
impedance (Zo) is outputted by the controller to a 12 bit DAC, the output of
which is fed to one of the inputs of differential amplifier with 'Z' as the other
input. The differential amplifier outputs □ Z(t) signal, which gives change in
impedance of the body segment as a function of time. It is low pass filtered,
provided programmable gain and limited to 5V amplitude and given to ADC input
of digital circuit. 'Z' is also used to obtain dZ/dt signal with the help of a
differentiator circuit (6). It is low pass filtered, provided programmable gain,
limited to 5 V & given to ADC input of digital card. The CAL/PAT relay and
selection of current value in the sine wave current source is controlled through the
micro-controller.
40. Figure 5 shows a preferred embodiment of the digital implementation of the
circuitry for generation of dZ/dt differentiated waveform. As seen in figure 4,
the Z-waveform (which is impedance waveform from the body) is differentiated
using Analog Differentiator and dZ/dt waveform is got, which is passed through
LPF and Programmable gain amplifier and then analog to digital converter in an
exemplary analog setup. This digital data is then given to micro controller and
which will use for process the data t o show as waveform on the screen and there
by calculate CO. In the digital circuitry, the Z-waveform is fed directly to ADC of
micro controller and converted to digital Z data waveform, which will be further
processed using software techniques to generate dZ/dt. Which is further
processed. Here again, the circuitry is made much simpler and Reliable.
2JL

41. The ECG is sensed from RA and LL of the patient with the help of surface
electrodes in order to provide synchronous pulse for ensemble averaging of the
IPG (impedance plethysmograph signal) signal. The signal is amplified with the
help of an isolation amplifier. 'R' wave of ECG or on set of 'CAL' signal is
detected with help of an adaptable threshold 'R' wave detector and TTL pulse
synchronous with (R' wave of ECG are obtained & connected to one of the input
port of Micro controller. The Analog ECG is also separately connected to one of
the ADC Channels. The Digital ECG will be used for displaying on the screen as
well to calibrate the ECG and also to check whether ECG Quality is good. The
digital card is connected to PC through serial communication link (RS232).
42. The selection of differential hardware parameter such as current amplifier (4mA/
2mA/ CAL), output waveforms (dZt, dZ/dt, N dZ/dt) and gain of the system
(1/2, 1 & 2) is performed with the help of user friendly menu driven program
running on the SBC.
Cardiac output measurement
43. Figure 6 shows the rate of change of impedance waveform. In order that the
cardiac output measurement happens, certain important points need to be selected
on the graph. The system provides two modes of measurement, namely, the
continuous mode of measurement and the intermittent mode of measurement.
Under the continuous mode of measurement, the system automatically selects the
important points of 'A', 'B', 'C and 'Xf'and subsequently calculates the cardiac
output measurement. In the intermittent mode of measurement, the clinician
operating the system must manually select the points using which the system will
subsequently do the calculation of cardiac output.
22-

44. To find the 'C' point a moving window of 'n=150' points is considered. A peak
point is found out, out of the selected window. All n/2 points on either side of the
peak point are compared for thrush hold of 75% of this peak point. If any point
crosses this limit then search for another peak will be carried out and that is
considered as another 'c' point. And n is re adjusted for n=n/4. thrush hold is
calculated as T= 75% of 'C' point. Calculate the HR using time difference between
two 'C 'points. Left side and right side of the 'C' point, n/2 samples will be taken
and lower most points out of these are considered as 'A' on back side and 'X' on
forward side. Once we have 'A' point take a point, which is app. 15% Equivalent
to the amplitude of difference of 'C' and 'A' point. This point is considered as 'B'
point. Take the amplitude value difference of 'C' and CB' this will become (dZ/dt)
max and the time difference of between 'X' and 'B' is considered as Lvet. Now we
can calculate beat-to-beat stroke volume.
45. Manual method of calculation of CO is provided to get accurate CO
measurement. This has got two advantages a) when the automated method fails to
locate the BCX point at proper the user can manual select the "A" point to get the
CO value. B) This also gives facility to select 'A' point at different places and do
research on the waveform. Here user need to select the 'A' point, which is lower,
most point left of 'Cy point. This will enable the unit to select the 'C' point (which
is the peak point of the waveform) and "X" point, which is lower most point on
the right side of the waveform. Once "A" point is selected the unit will use the
Algorithm mentioned in the point number one to calculate the CO. This method
been validated against the gold standard technique available in the market today.
("Tran thoracic electrical bio-impedance for non-invasive measurement of cardiac
output: Comparison with Thermo dilution, Echocardiography and radioisotope
method", A collaborative study between National Institute of Metal Health &
Neurosciences, Bangalore, India & Narayan Hrudayalay- A premier Institute of
cardiology, Bangalore, India).
Z3

46. In the preferred embodiment of the present invention, the patient information and
waveforms can be stored with unique name, can be retrieved for reanalysis and
stored. This can also be connected to USB printer and print can be taken on
normal A4 size paper. It allows user to store more than 1,000 patient data under
the unique name.
47. The system of the invention provides several advantages over prior art systems
and methods. Existing prior art systems also use the same working principle i.e.
impedance cardiography. However, these prior art systems use a dedicated PC
system for the computation and display of the related waveforms and display of
digital values. Such systems while user friendly, need significandy higher level of
inter-connections between the actual acquisition hardware and the PC. The system
of the invention is capable of being hooked up to the subject since it has an in
built acquisition hardware along with an industrial PC motherboard, thus avoiding
all the extra connections. The system of the invention is stand alone and PC based
monitor for measurement of cardiac output using a non invasive technique. The
application of the cardiac plethysmography technique was limited in respect of a
continuous monitoring system in critically ill patients was restricted due to the
complicated inter-connections between the acquisition hardware and PC. This
simplifies the level of sophistication required for an operator of the system.
48. The system of the invention avoids the problems of the prior art since all the
necessary hardware for signal acquisition and display has been assembled in a
single chassis. The user only needs to hook up the patient to the monitor to get
the required waveform on the screen along with the digital values. Also the
monitor can be used as a dedicated PC system just by connecting a mouse and a
keyboard to it (for which connectors have been provided in the side panel). The
overall size of the system is 25% of that of a conventional system (standalone PC
and the acquisition hardware). The system also provides for continuous and

Documents:

304-CHE-2006 EXAMINATION REPORT REPLY RECIEVED 17-02-2011.pdf

304-CHE-2006 FORM-1 22-02-2012.pdf

304-CHE-2006 FORM-13 22-02-2012.pdf

304-CHE-2006 POWER OF ATTORNEY 20-01-2012.pdf

304-CHE-2006 POWER OF ATTORNEY 22-02-2012.pdf

304-CHE-2006 AMENDED PAGES OF SPECIFICATION 22-02-2012.pdf

304-CHE-2006 AMENDED CLAIMS 17-02-2011.pdf

304-CHE-2006 AMENDED CLAIMS 22-02-2012.pdf

304-CHE-2006 AMENDED PAGES OF SPECIFICATION 17-02-2011.pdf

304-CHE-2006 AMENDED PAGES OF SPECIFICATION 10-04-2012.pdf

304-CHE-2006 CORRESPONDENCE OTHERS 02-03-2012.pdf

304-CHE-2006 CORRESPONDENCE OTHERS 20-01-2012.pdf

304-CHE-2006 CORRESPONDENCE OTHERS 22-02-2012.pdf

304-CHE-2006 CORRESPONDENCE OTHERS 10-04-2012.pdf

304-CHE-2006 OTHER PATENT DOCUMENT 10-04-2012.pdf

304-che-2006-abstract.pdf

304-che-2006-claims.pdf

304-che-2006-correspondence-others.pdf

304-che-2006-correspondence-po.pdf

304-che-2006-description(complete).pdf

304-che-2006-drawings.pdf

304-che-2006-form 1.pdf

304-che-2006-form 5.pdf

304-che-2006-form 9.pdf


Patent Number 252030
Indian Patent Application Number 304/CHE/2006
PG Journal Number 17/2012
Publication Date 27-Apr-2012
Grant Date 23-Apr-2012
Date of Filing 24-Feb-2006
Name of Patentee LARSEN & TOUBRO LIMITED
Applicant Address MYSORE WORKS, HAVING OFFICE AT KIADB INDUSTRIAL AREA, HEBBAL - HOOTAGALLI, MYSORE - 570 018.
Inventors:
# Inventor's Name Inventor's Address
1 VISHWANANT.P. NAYAK LARSEN & TOUBRO LIMITED MYSORE WORKS, HAVING OFFICE AT KIADB INDUSTRIAL AREA, HEBBAL - HOOTAGALLI, MYSORE - 570 018.
2 TEJAS BENGALI LARSEN & TOUBRO LIMITED MYSORE WORKS, HAVING OFFICE AT KIADB INDUSTRIAL AREA, HEBBAL - HOOTAGALLI, MYSORE - 570 018.
PCT International Classification Number A61B 5/0295
PCT International Application Number N/A
PCT International Filing date
PCT Conventions:
# PCT Application Number Date of Convention Priority Country
1 NA