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陽明大學附設醫院
心臟內科 黃嵩豪
First External Stimulation
Catharina Serafin
Increase in heart rate (140 bpm)
Hugo von Ziemssen (1882)
Stimulation: ON OFF
Right Ventricle
Left Ventricle
1827/46 Bradycardia as cause of syncope
(Adams, Stokes)
1882 First external stimulation (von Ziemssen)
1932 First external pacemaker (Hyman)
1952 External stimulation via surface electrodes
(Zoll)
1958 External stimulator with transvenous lead
(Furman, Robinson)
1958 First implantable PM with transvenous lead
(Elmquist, Senning)
Historical Milestones
First External Pacemaker Hyman (1932)
- Clockwork generator with manual power
- Transthoracic stimulation needle
- Handle turn to provide induction stimulus
Cardiac standstill
Stimulation 120 ppm
Transvenous External PM Furman and Robinson (1958)
Wearable Pulse Generator - Around Waist (1958 )
First Implantable Pacemaker Senning and Elmquist (1958)
Rune Elmquist
Engineer at Siemens-Elema
Ake Senning, Cardiac Surgeon
Karolinska Hospital Stockholm
First Implantable Pacemaker Senning and Elmquist (1958)
• 2 Transistors
• Pulse 2 V / 1.5 ms
• Rate 80 ppm
55 mm Ø , 16 mm thick
First Pacemaker Patient: Arne Larsson
1986
First Implantable Pacemaker
First Battery Powered PM
Chardack, Greatbatch (1960)
10 Zinc-Mercury Batteries
First Programmable PM Chardack, Greatbatch (1963)
with a screwdriver
Founded in 1949 as a
medical equipment
service company
History and Background History
• First external wearable pacemaker
Success With Implantable Pacemakers
In the United States, the first successful attempts at designing a totally implantable pacemaker were reported by Drs. William Chardack and Andrew Gage at the Veterans Administration Hospital in Buffalo, New York, and Wilson Greatbatch, an electrical engineer. The three men carried out more than two years of experimental work and testing, then published a paper about their work in 1960.
Medtronic's founders read the article with interest and soon contacted the New York researchers. Palmer Hermundslie flew his own plane to Buffalo to meet Dr. Chardack and Greatbatch, and signed a contract giving Medtronic exclusive rights to produce and market the Chardack-Greatbatch implantable pulse generator. Within two months of beginning production in late 1960, Medtronic had received orders for 50 of the $375 implantable units.
Co-founder Palmer Hermundslie often piloted his own plane to make emergency deliveries of pacemakers.
At the same time, Medtronic appointed Picker International Corporation of White Plains, New York, as its sole distributor outside the United States, exclusive of Canada. Picker's 72 foreign sales offices greatly expanded the marketing efforts of Medtronic, which had 14 sales representatives covering the United States and Canada.
In addition to the implantable pacemaker, the representatives sold seven other Medtronic products, including the Telecor, which visibly and audibly monitored heart activity; the Cardiac Sentinel, an automatic alarm that summoned aid when the patient's heart activity became critical and stimulated the heart with an electronically regulated pulse; and a Coagulation Generator, used to control bleeding during surgery without damaging nearby tissue.
Dr. C. Walton Lillehei with a child who received one of the early Medtronic external pacemakers
Atomic Pacemaker Plutonium powered PM (1967)
Implantable Electronic Cardiac Devices Historical Aspects
1932 1958 1964 1970 1980’s 1994
Hyman
Senning and Elmquist
1st implant of an electronic
PM
Mirowski
Development of the 1st ICD – implant in dogs
1st report of CRT
RECENTLY
Furman
1st endocardiac PM
Heart Failure control
Home Monitoring
Basic Concept of Pacemaker Over view
- Pacemaker System
- Pacemaker Function
- NBG Code
- Lead Impedance
- The magnet Mode & Electromagnetic Interference
- Information for patient ‘s pacemaker
What is a pacemaker ?
A device for increaseing a slow HR
A device used primarily to correct some types of bradycardia, or slow heart rhythms.
Who need it ?
Indications for Pacing
Sick Sinus Syndrome
Heart Block
Post RF Ablation
How does it work ? Attach the pacemaker system
Pulse generator
Sensing and Pacing leads
Make it into a circuit
Put the system into the body / under the skin and join to the
heart by pacing wire
Program it’s function by the programmer
Pacing Systems Pulse generator
Sensing and Pacing lead
The Pacemaker System
Patient
Lead
Pacemaker
Programmer
Lead
Pacemaker
Leads
Epicardial
Endocardial
Connection to Pacemaker
Just a Simple Lead
Lead System
A lead is the insulated wire used to connect the pulse
generator to the cardiac tissue
The lead transmits the energy to the myocardium and
relays intrinsic cardiac signals back to the sensing
circuit
Components of a Pacing Lead
Connector
Proximal Ring
Electrode
Lead
Body Active Fixation
Mechanism
Suture
Sleeve
Distal Tip
Electrode
Fixation Mechanisms
Active fixation Screw-in lead
Passive fixation Tined tip
Passive fixation Finned tip
Suture On
Sutureless
Epicardial Leads
Pacemaker Circuit
Unipolar VS Bipolar
Bipolar
Unipolar
Unipolar Vs. Bipolar
+ + -
Unipolar Configuration
Lead
Pacemaker Unipolar Pathway
-
+
Bipolar Configuration
Lead
Pacemaker
-
+
Bipolar Pathway
Unipolar Versus Bipolar
UNIPOLAR vs BIPOLAR
Unipolar Leads
Advantage
Smaller size
Easier to implant?
Larger spike on surface ECG
Theoretically more reliable
Disadvantages
Possibility of pocket stimulation
Possibility of myopotential inhibition
Susceptible to EMI
Susceptible to cross-talk
Bipolar Leads
Advantages
Torque control
Noise Rejection
Programming flexibility
No Pocket stimulation
Disadvantages
Larger Diameter
Stiffer
Small ECG Artifact in surface ECG
Lead Placement
Ventricular Lead
Right Ventricular Apex (RVA) or Right Ventricular Outflow Tract (RVOT) Ventricular Bradycardia Pacing
Sensing Intrinsic Rhythm
Atrial Lead
Right Atrial Appendage or Atrial Septal Wall Atrial Pacing
Atrial Sensing
Ventricular Lead Placement
Atrial Lead Placement
The atrial lead should be implanted on the septal wall of the atrial appendage
Once the lead is in the proper position it will have a “wagging” appearance
Atrial Endocardial Placement
Single Chamber Pacing
One Lead
One Circuit / Pacemaker
One Patient
Dual-Chamber Pacing
Basic Function
Energy
Output Parameters
Cardiac Stimulation Threshold
Impedance
Energy
Ohm's Law
Voltage
Current
Resistance
How to stimulate?
Ohm s Law: V = R x I
R = V
I
Voltage
Current = =
[V]
[A]
The higher the voltage and the lower the resulting current
the higher is the resistance.
V = Voltage, I = Current , R = Resistance
Voltage
The difference in potential energy between two points
Unit of measure = volt (V)
Current
The rate of transfer or flow of electricity
Unit of measure – milliampere (mA)
Resistance
The opposition to the flow of electrical current through a material
Unit of measure = ohm (Ω)
V = IR
V = IR
CONSTANT VOLTAGE
t (ms)
How to stimulate?
Pulse
Amplitude
Pulse Duration
U (V)
Pacemaker Pulse
Pacing Technology “Secret”
Pacemakers do only 2 things:
Pace
Sense
Capture
Definition : Cardiac depolarization and resultant contraction caused by pacemaker stimulus
Pacing (Stimulation) threshold
The lowest amount of energy to capture the myocardium 100 % of the time
How to stimulate?
Pulse Duration (ms)
Pulse
Ampli-
tude
(V)
Pulse Duration (ms)
Pulse
Ampli-
tude
(V)
How to stimulate?
Rheobase - Chronaxie
How to stimulate?
Pulse Duration (ms)
Pulse
Ampli-
tude (V)
Energy
(mJ)
How to stimulate?
E = R x I x t
E = x t (Joule) V2
R
Energy
V = R x I
V
R I =
E = V x x t V
R
How to stimulate?
E = x t (J) V2
R Energy
How to save energy?
- lower pulse amplitude (V²)
- lower pulse duration
- high impedance
Strength Duration Curve
pulse width (msec)
Voltage t
hre
shold
(V
)
Chronaxie
Rheobase
2 x Rheobase Most efficient pulse width
• The rheobase is the least voltage needed to
depolarise the heart at an infinite pulse duration.
• The chronaxie is the shortest pulse duration
required to depolarise the heart at a voltage twice
the rheobase.
Pacing Thresholds
Suggested Intraoperative Values
Atrium
Less than 1.5 Volts
Ventricular
Less than 1.0 Volts
Pacing Impedance
300-1500 Ω Depending on lead type
Acute To Chronic Threshold Change
Historically reported to occur between 2-8 weeks post implant
Thresholds may increase 2-5 times
Virtual Electrode - Myocardial Interface
Excitable Tissue
Non-Excitable Tissue
Virtual Electrode
Electrode
Chronic Electrode
Pacing Thresholds
Hayes, D. et. al. Cardiac Pacing and Defibrillation: A Clinical Approach.
Futura. Armonk, NY. 2000:7.
0
0.5
1
1.5
2
2.5
3
3.5
4
4.5
5
1 2 3 4 5 6 7 13 26 52
Time After Implant
Ch
ron
ic P
ac
ing
Th
res
ho
ld,
Pu
lse
Wid
th (
ms)
0
0.5
1
1.5
2
2.5
3
3.5
4
4.5
5
1 2 3 4 5 6 7 13 26 52
Time After Implant
Ch
ron
ic P
ac
ing
Th
res
ho
ld,
Pu
lse
Wid
th (
ms)
Steroid
No Steriod
Sensing
Definition: The ability of the pacemaker to sense an intrinsic electrical signal
Sensing
When programming sensitivity, as you lower the number you make the pacemaker more sensitive, (allow it “see” more).
1 mV 2 mV 5 mV
Sensing
Sensing
Sensing Threshold: indicates the minimum intracardiac signal that will be sensed by the pacemaker to initiate the pacemaker response (inhibited or triggered)
Sensing
X
= programmed
sensitivity
Amplifier
and Filter
Signal
processing
Signal
recording
How to sense?
0
5
10
15
20
25
1 3 5 10 30 50 100 300 1000
VES
R-wave
T-wave
Amplitude
Frequency (Hz)
P-wave Myopotentials
(mV)
How to sense?
Filtering of Intracardiac Signals
How to sense?
Sensitivity: 2.5 mV
Vs Vs
0
5
5
Intra-
cardiac
Signal
(mV)
Vs Vs Vs Vs
PM Marker
How to sense?
Sensitivity: 5.0 mV
Intra-
cardiac
Signal
(mV)
PM Marker
0
5
5
Vs Vs
Undersensing
Sensing Thresholds
Suggested Intraoperative Values
Atrium
Greater than 2.0 mV
Ventricular
Greater than 5.0 mV
The NASPE/BPEG Generic (NBG) Code
Position
Category
Letters Used
Manufac- turer’s Designation Only
I II III
Chamber(s) Paced
Chamber(s) Sensed
Response to Sensing
Rate modulation Multisite pacing
O-None P-Simple
Programmable
M-Multi- Programmable
C-Communicating R-Rate
modulation
O-None A-Atrium V-Ventricle D-Dual
(A+V)
S- Single (A or V)
S- Single (A or V)
O-None A-Atrium V-Ventricle D-Dual
(A+V)
O-None T-Triggered I-Inhibited D-Dual
(T+I)
O-None A-Atrium V-Ventricle D-Dual
(A+V)
IV V
Version 2001
Insulation Break Current is escaping
Decreased Resistance
Increased Current Drain
Pacing and sensing problems
Lead Fracture
Current cannot reach heart
Increased Resistance
Decreased Current Drain
Pacing and sensing problems
LiJ - Battery
Hybrid
Connectors
Titanium
housing
Components of the PM
Pacemaker Programming
Telemetry
Antenna
Pacemaker Power Source
Zinc-Mercury Lithium-Iodine
Pacemaker Power Source
Zinc-Mercury Lithium-Iodine
Time Time
Pacemaker Power Source
Pacemaker Power Source
Pulse Amplitude and Device Longevity Battery 1.1 Ah
Mode VVI VVI DDD DDD Amplitude (V) 5 2.5 5 2.5
Inhibited (µA) 11 11 12 12
Pacing V (µA) + 10 + 2,5 + 10 + 2,5
Pacing A (µA) - - + 10 + 2,5 Total (µA) 21 13,5 32 17
Longevity (yrs) 6,2 9,6 4,1 8,0
Lead Resistance/Impedance Changes
High Resistance
> 2500 ohms
Also called an “Open Circuit”
Chronic lead system
Fractured lead conductor coil
Acute lead system
Loss of contact between the terminal pin of the lead and the pacemaker header set screw
Low Resistance
< 250 ohms
Also called “Shorted Circuit”
Insulation Break-Down
Insulation cut by suture
Degradation of the insulation
Subclavian Crush Syndrome
Lead Resistance/Impedance
Changes
Implantable Cardioverter Defibrillator Anti-tachycardia Devices
First graphic documentation of ventricular fibrillation
ICD Evolution: 1850
Carl Ludwig (1816-1895)
1st documented termination of VF with elevated current
Their work went largely unnoticed for 30 years
ICD Evolution: 1899
• Reproduced electric current
termination of VF
• Done at the request of Bell
telephone to address
electrocution of line workers
(occurring at the rate of 1000/yr)
ICD Evolution: 1930
William Kouwenhoven (1886-1975)
What is ICD Therapy? • ICD therapy consists of
pacing, cardioversion, and
defibrillation therapies to
treat tachyarrhythmias. ICDs
also have programmable
diagnostic functions.
• An ICD system includes the
device, and the pacing,
sensing and defibrillation
lead(s).
1947
• First successful
defibrillation of
exposed human
heart
• Required
thoracotomy
ICD Evolution:
Early Medtronic Defibrillator 1950’s
Used in open heart surgeries
Applied directly to the heart
ICD Evolution
1970 • Patent granted for
first totally implantable defibrillator
• System used an intracardiac catheter and SQ patch with detection via RV pressure transducer
ICD Evolution
Michael Mirowski (1924-1990)
ICD Evolution
NEJM 1997;337;1576-83
Secondary Prevention of Sudden Arrhythmic Death
AVID Study
N of Patients at Risk ICD 742 502 (0.91) 274 (0.84) 110 (0.78) 9 Conventional 490 329 (0.90) 170 (0.78) 65 (0.69) 3
Moss AJ. N Engl J Med 2002;346:877-883
ICD
Conventional P = 0.007
1.0
0.9
0.8
0.7
0.6
0.0
Surv
ival
Pro
bab
ility
0 1 2 3 4 Years
0.78
0.69 -31%
Primary Prevention of Sudden Arrhythmic Death
MADIT II Study
Cardiac Resynchronization Therapy for Heart Failure
Ventricular Dysynchrony and Cardiac Resynchronization
• Ventricular Dysynchrony1 – Electrical: Inter- or
Intraventricular conduction delays typically manifested as left bundle branch block
– Structural: disruption of myocardial collagen matrix impairing electrical conduction and mechanical efficiency
– Mechanical: Regional wall motion abnormalities with increased workload and stress—compromising ventricular mechanics
• Cardiac Resynchronization
– Therapeutic intent of atrial synchronized biventricular pacing
• Modification of interventricular, intraventricular, and atrial-ventricular activation sequences in patients with ventricular dysynchrony
• Complement to optimal medical therapy
1 Tavazzi L. Eur Heart J 2000;21:1211-1214
Prevalence of Inter- or Intraventricular Conduction Delay
1 Havranek E, Masoudi F, Westfall K, et al. Am Heart J 2002;143:412-417 2 Shenkman H, McKinnon J, Khandelwal A, et al. Circulation 2000;102(18 Suppl II): abstract 2293 3 Schoeller R, Andersen D, Buttner P, et al. Am J Cardiol. 1993;71:720-726 4 Aaronson K, Schwartz J, Chen T, et al. Circulation 1997;95:2660-2667 5 Farwell D, Patel N, Hall A, et al. Eur Heart J 2000;21:1246-1250
IVCD 15%
IVCD >30%
General HF Population1,2
Moderate to Severe HF Population3,4,5
60%
70%
80%
90%
100%
0 60 120 180 240 300 360
Days in Trial
Cu
mu
lati
ve
Su
rviv
al
QRS Duration (msec)
<90
90-120
120-170
170-220
>220
Wide QRS – Proportional Mortality Increase
• NYHA Class II-IV patients
• 3,654 ECGs digitally scanned
• Age, creatinine, LVEF, heart rate, and QRS duration found to be independent predictors of mortality
• Relative risk of widest QRS group 5x greater than narrowest
1 Gottipaty V, Krelis S, Lu F, et al. JACC 1999;33(2) :145 [Abstr847-4].
Vesnarinone Study1 (VEST study analysis)
Clinical Consequences of Ventricular Dysynchrony
• Abnormal interventricular septal wall motion1
• Reduced dP/dt3,4
• Reduced pulse pressure4
• Reduced EF and CO4
• Reduced diastolic filling time1,2,4
• Prolonged MR duration1,2,4
1 Grines CL, Bashore TM, Boudoulas H, et al. Circulation 1989;79:845-853. 2 Xiao, HB, Lee CH, Gibson DG. Br Heart J 1991;66:443-447. 3 Xiao HB, Brecker SJD, Gibson DG. Br Heart J 1992;68:403-407. 4 Yu C-M, Chau E, Sanderson JE, et al. Circulation. 2002;105:438-445.
Click to Start/Stop
Longer
Shorter
Relaxed
Courtesy of Dr Kass, MD, Johns Hopkins University, Maryland.
SEPTUM BASE
APEX
SEPTUM BASE
Normal Dilated Cardiomyopathy
APEX
Left Ventricular Dysfunction Electromechanical Dyssynchrony
Summary of Proposed Mechanisms
Yu C-M, Chau E, Sanderson J, et al. Circulation 2002;105:438-445
Intraventricular
Synchrony
Atrioventricular
Synchrony
Interventricular
Synchrony
LA
Pressure
LV Diastolic
Filling
RV Stroke
Volume
LVESV LVEDV
Reverse Remodeling
Cardiac Resynchronization
MR
dP/dt, EF, CO
( Pulse Pressure)
Proposed Mechanisms: Improved Intraventricular Synchrony
Kass D Chen-Huan C, Curry C, et al. Circulation 1999;99:1567-73
PV loop tracings at right illustrate BiV/LV pacing produces: greater stroke work (area) and increased stroke volume (width), and a reduced systolic volume
0
40
80
120
0 100 200 300
0
40
80
120
0 100 200 300
0
40
80
120
0 100 200 300
0
40
80
120
0 100 200 300
LV
Pre
ss
ure
(m
m H
g)
LV
Pre
ss
ure
(m
m H
g)
LV Volume (mL) LV Volume (mL)
RV Apex RV Septum
LV Free Wall Biventricular
----- NSR Control - - - VDD Pacing
Adapted from Kass et al.
Proposed Mechanisms: Improved Intraventricular Synchrony
Click to Start/Stop
dP/dt 1,3,4 EF1,5
Pulse Pressure 3,4 SV&CO1, 2
Improved Intraventricular
Synchrony1,2
MR1
LVESV1
LA
Pressure1
1 Yu C-M, Chau E, Sanderson J, et al. Circulation 2002;105:438-445 2 Søgaard P, Kim W, Jensen H, et al. Cardiology 2001;95:173-182 3 Kass D Chen-Huan C, Curry C, et al. Circulation 1999;99:1567-73 4 Auricchio A, Ding J, Spinelli J, et al. J Am Coll Cardiol 2002;39:1163-1169 5 Stellbrink C, Breithardt O, Franke A, et al. J Am Coll Cardiol 2001;38:1957- 65
Proposed Mechanisms: Improved Atrioventricular Synchrony
Click to Start/Stop
1 Yu C-M, Chau E, Sanderson J, et al. Circulation 2002;105:438-445 2 Kindermann M, Frohlig G, Doerr T, et al. Pacing Clin Electrophysiol 1997; 20(I):2453-2462 3 Breithardt O, Stellbrink C, Franke A, et al. Am Heart J 2002;143:34-44 4 Søgaard P, Kim W, Jensen H, et al. Cardiology 2001;95:173-182
Improved Atrioventricular
Synchrony
LA1 Pressure
LV Diastolic Filling1,3
LVEDV1,4
Optimized AV Delay: Isovolumic Contraction Time1,2
MR1,4
1 Yu C-M, Chau E, Sanderson J, et al. Circulation 2002;105:438-445 2 Kerwin W, Botvinick E, O’Connel W, et al. JACC 2000;35:1221-7
Improved Interventricular
Synchrony1,2
LV Diastolic
Filling1
RV Stroke
Volume1
Courtesy of Ottawa Heart Institute
LV Wall
Endocardium
RV
Septum
LV
Proposed Mechanisms: Improved Interventricular Synchrony
Achieving Cardiac Resynchronization Mechanical Goal: Atrial-synchronized bi-ventricular pacing
• Transvenous Approach
– Standard pacing lead in RA
– Standard pacing or defibrillation lead in RV
– Specially designed left heart lead placed in a left ventricular cardiac vein via the coronary sinus
Right Atrial
Lead
Right Ventricular
Lead
Left Ventricular
Lead
Cardiac Resynchronization Atrio-biventricular Pacing
LV RV
Cleland et al, Eur Heart J 2006;27(16):1928-32
0 500 1000 1500 0
25
50
75
Days
P<0.0001 Event-
free S
urv
ival
5 71 192 321 365 404 8 89 213 351 376 409
Control
CRT
N of Patients at Risk
Medical Therapy
CRT
100 HF CF III/IV
EF<0.35
QRS>130ms
Cardiac Resynchronization
CARE-HF Study: Overall Mortality
Cardiac Resynchronization
CARE-HF Study: Sudden Mortality
Cleland et al, Eur Heart J 2006;27(16):1928-32
CRT
Medical Therapy
Su
rviv
al
Time (days)
Hazard ratio 0.54
(95% CI 0.35-0.84. P = 0.006)
CRT = 32 sudden deaths (7.8%)
Medical therapy = 54 sudden deaths (13.4%)
1.00
0.75
0.50
0.25
0.00
0 400 800 1200 1600
Cardiac Resynchronization + ICD
COMPANION Study: Overall Mortality
N Engl J Med 2005
CRT-D
CRT
TMO
Sobre
vid
a liv
re d
e e
vento
s (
%)
19%
12%
15%
N:1520