**Past, Present and Future Catheter Technologies and Energy Sources for Atrial Fibrillation Ablation**

Inderpal Singh, Adam Price, Zachary Leshen and Boaz Avitall *University of Illinois at Chicago, IL USA* 

#### **1.Introduction**

30 Will-be-set-by-IN-TECH

186 Electrophysiology – From Plants to Heart

Simmons W. N., Mackey S., He D. S. & Marcus F. I. (1996). Comparison of gold versus

SippensGroenewegen A., Roithinger F. X., Peeters H. A., Linnenbank A. C., van Hemel N. M.,

Tilg B., Fischer G., Modre R., Hanser F., Messnarz B., Schocke M., Kremser C., Berger T.,

excitation in humans, *IEEE Transactions on Medical Imaging* 21(9): 1031–1039. Tilg B., Hanser F., Modre-Osprian R., Fischer G., Messnarz B., Berger T., Hintringer F.,

Tilg B., Renhardt M., Fleischmann P. & Wach P. (1992). Modellierung der

Wach P., Modre R., Tilg B. & Fischer G. (2001). An iterative linearized optimization

Wach P., Tilg B., Lafer G. & Rucker W. (1997). Magnetic source imaging in

electrical excitation, *Journal of Electrocardiology* 35(4, part B): 81–87.

*Biomedizinische Technik/Biomedical Engineering* 37(s1): 33–35.

*Electrical and Electronic Engineering* 20(3): 676–688.

35(3): 157–166.

*Computer-Assisted Intervention*, Vol. 2, St. Malo, France, pp. 502–509.

*and Clinical Electrophysiology* 19(4): 398–402.

*Journal of Electrocardiology* 31(Suppl.): 85–91.

*intervention: MICCAI ... International Conference on Medical Image Computing and*

platinum electrodes on myocardial lesion size using radiofrequency energy, *Pacing*

Steiner P. R. & Lesh M. D. (1998). Body surface mapping of atrial arrhythmias: atlas of paced p wave integral maps to localize the focal origin of the right atrial tachycardia,

Hintringer F. & Roithinger F. X. (2002). Model-based imaging of cardiac electrical

Pachinger O. & Roithinger F. X. (2002). Clinical ECG mapping and imaging of cardiac

Leitfähigkeitsanisotropie im Herzen zur EKG- und MKG-berechnung,

technique for non-linear ill-posed problems applied to cardiac activation time imaging, *COMPEL: The International Journal for Computation and Mathematics in*

the human heart: estimating cardiac electrical sources from simulated and measured magnetocardiogram data, *Medical and Biological Engineering and Computing* Atrial fibrillation (AF) is one of the most common tachyarrhythmias, with an incidence that continues, especially among the elderly where it affects upto 7% of the population. Due to the associated morbidities, including the risk of stroke, heart failure and impaired quality of life, numerous modalities have emerged for the treatment of atrial fibrillation. In recent years, an increasing number of patients are being treated with catheter ablation in an effort to restore sinus rhythm and decrease the associated co-morbidities. Compared to other treatment modalities, primarily that of pharmacotherapy, ablation of AF offers the unique opportunity to restore sinus rhythm and its associated benefits without the associated risks of anti-arrhythmic medications. These benefits, however, must be weighed against the known risks of ablation, which include perforation, cardiac tamponade, pulmonary vein stenosis and esophageal injury. It has been well described previously that premature atrial contractions (PACs) originating from the pulmonary veins are an important trigger for the initiation of AF. The sources of these PAC s are believed to be related to the presence of left atrial myocardial tissue that extends into the pulmonary vein. Consequently, most ablation strategies attempt to achieve electrical isolation of the pulmonary veins for the treatment of paroxysmal AF. Different energy sources combined with innovative catheter technologies are likely to improve the success rates of AF ablation.

#### **2. Radiofrequency lesions**

Radiofrequency (RF) energy is currently the most widely used energy source for performing catheter ablation procedures. RF generators deliver alternating current at frequencies too high to depolarize the myocardium between 500 and 1000 KHz (Haines 1993 and Skanes et al 2003). When using a 4mm catheter ablation tip, the radiofrequency energy used (20 to 50 W) is often generated from a 550 KHz electrosurgical unit and is delivered for 30-120 seconds (Manolis et al 1994). Most commonly the RF power is delivered between a 8F 4-8mm catheter ablation tip and a dispersive reference patch applied to the skin. The application of RF energy between the small ablation tip and the dispersive electrode results in the greatest resistance to the current flow at the catheter tip to tissue interface. This results in resistive heating, and consequently leads into lesion

Past, Present and Future Catheter Technologies

**3. Irrigated tip catheter with contact sensor** 

al 2009)

lesion.

**4. Spiral catheter** 

and Energy Sources for Atrial Fibrillation Ablation 189

Fig. 1. Irrigated closed loop and open irrigation electrode catheter (Yokoyama et al 2006).

RF ablation is dependent on good tissue contact where the ablation electrode is firmly embedded in the targeted tissue. The contact angle and the force between the tip of the catheter and the tissue surface play a major role in the characteristics of the lesion. Irrigated tip catheters with contact sensors can be used to estimate the contact force and angle (Figure 2). The catheter tip in this case is equipped with a deformable body that makes contact with the myocardial tissue. When subject to contact forces exerted by the tissue, the deformable body translates these forces into changes in wavelengths by optical fibers present within the catheter. Ultimately, these changes in wavelength are transformed via a computer algorithm to display both catheter vectors as well as contact force. The benefit of this catheter is that the combination of appropriate angle and force can be used to generate maximum transmurality with minimum incidence of steam pop and thrombus formation. (Schmidt et

Another example of a catheter that is designed to specifically isolate the pulmonary vein (PV) Ostia resembles a corkscrew shape (Figure 3). This catheter is equipped with four 12 mm coil electrodes, with two thermistors placed at the edges of each coil to regulate the RF power, adjusting to the maximal sensed temperature from each thermistor (Avitall et al

The ablation catheter is introduced into the PVs via a 9F sheath. Once the tip of the catheter is in the PV, the sheath is withdrawn while maintaining the catheter position in the PV. As shown below, the spiral catheter expands within the vein and the coil electrodes are embedded within and under the orifice of the PV [figure 4]. Prior studies using this catheter demonstrated no visible PV narrowing during final PV angiography. PV circumferential lesions were documented in PVs and no PV stenosis was documented. One drawback however was the requirement to rotate the catheter position to create a circumferential

2005). Standard radiofrequency generator with specialized interface was used.

formation at the catheter to tissue interface. Deep tissue heating is consequence of conductive heating which is responsible for deep lesion formation. Conductive heating diminishes as a function of 1/r4 where 'r' equals the distance from the point of maximal resistive heating (Hoffmann et al 1992 and Avitall et al 2004). Tissue temperatures above 45 °C result in increase in cytosolic calcium concentration due to increased permeability, while sarcoplasmic ATPase is inhibited at temperatures above 50°C. Above 50°C, irreversible tissue damage has been documented (Haines DE 1993 and Inesi et al 1973). At 60°C, collagen denaturation occurs, with loss of elasticity and compliance of the ablated tissues.

#### **2.1 RF ablation non irrigated tip catheter**

The depth of lesion size increases as the temperature increase at the interface up to 100C. Above this temperature, the plasma starts boiling resulting in coagulum formation at the tip. This can lead to clot embolization, a sudden increase in impedance, loss of thermal conductivity, and ineffective tissue heating. Non-irrigated catheters are available with 4- 5mm and 8mm length tip ablation electrodes with an integrated thermocouple to monitor the tip temperature. With the 8mm catheter, a large portion of the electrode is exposed to flowing blood which cools the tip allowing for the application of higher RF power and the creation of larger lesions.

A thermocouple is integrated at the tip for monitoring the temperature during ablation. The new generation RF generators can help to titrate the power up and down until the desired tip temperature is reached. This is called temperature guided RF ablation (Skanes et al, 2003). Nowadays the generators are capable of opting between temperature guided or power guided RF ablation. The risk of a thromboembolism after LARFA (Left atrial radiofrequency ablation) is 1.1%, with most events occurring within 2 weeks after the procedure using 8mm tip catheter. (Oral et al 2006)

#### **2.2 Irrigated tip electrode catheter**

The irrigated tip electrode catheter (Figure 1) has 4-5mm ablation electrode. The presence of irrigation helps to keep the temperature at the tissue-electrode interface lower, thereby permitting improved delivery of RF energy to deeper tissues. Ultimately, this can facilitate the creation of more complete, and transmural, radiofrequency lesions. Additionally, irrigation at the site of ablation has also helped to minimize thrombus formation at the ablation site as well. The saline used for irrigation can be circulated within the electrode (closed loop system), or open irrigation system that flushes saline through openings in the ablation electrode (Budde et al 1987, Grumbrecht et al 1998, Kongsgaard et al 1997, matsudairi et al 2003, Nakagawa et al 1998, Wittkampf et al 1989 and Yokoyama et al 2006). A major limitation of this catheter is the poor correlation of the tip temperature with the tissue temperature, often resulting in RF being curtailed and therefore incomplete lesions are made. The incidence of silent thromboembolic event in post ablation atrial fibrillation patients is 8.3% in irrigated tip catheter, 38.9% in duty cycled multielectrode catheter and 5.6% in cryoballoon (Gaita et al 2011). The duty cycled and cryoballoon ablation catheters have further been explained in the chapter.

formation at the catheter to tissue interface. Deep tissue heating is consequence of conductive heating which is responsible for deep lesion formation. Conductive heating diminishes as a function of 1/r4 where 'r' equals the distance from the point of maximal resistive heating (Hoffmann et al 1992 and Avitall et al 2004). Tissue temperatures above 45 °C result in increase in cytosolic calcium concentration due to increased permeability, while sarcoplasmic ATPase is inhibited at temperatures above 50°C. Above 50°C, irreversible tissue damage has been documented (Haines DE 1993 and Inesi et al 1973). At 60°C, collagen denaturation occurs, with loss of elasticity and compliance of the ablated

The depth of lesion size increases as the temperature increase at the interface up to 100C. Above this temperature, the plasma starts boiling resulting in coagulum formation at the tip. This can lead to clot embolization, a sudden increase in impedance, loss of thermal conductivity, and ineffective tissue heating. Non-irrigated catheters are available with 4- 5mm and 8mm length tip ablation electrodes with an integrated thermocouple to monitor the tip temperature. With the 8mm catheter, a large portion of the electrode is exposed to flowing blood which cools the tip allowing for the application of higher RF power and the

A thermocouple is integrated at the tip for monitoring the temperature during ablation. The new generation RF generators can help to titrate the power up and down until the desired tip temperature is reached. This is called temperature guided RF ablation (Skanes et al, 2003). Nowadays the generators are capable of opting between temperature guided or power guided RF ablation. The risk of a thromboembolism after LARFA (Left atrial radiofrequency ablation) is 1.1%, with most events occurring within 2 weeks after the

The irrigated tip electrode catheter (Figure 1) has 4-5mm ablation electrode. The presence of irrigation helps to keep the temperature at the tissue-electrode interface lower, thereby permitting improved delivery of RF energy to deeper tissues. Ultimately, this can facilitate the creation of more complete, and transmural, radiofrequency lesions. Additionally, irrigation at the site of ablation has also helped to minimize thrombus formation at the ablation site as well. The saline used for irrigation can be circulated within the electrode (closed loop system), or open irrigation system that flushes saline through openings in the ablation electrode (Budde et al 1987, Grumbrecht et al 1998, Kongsgaard et al 1997, matsudairi et al 2003, Nakagawa et al 1998, Wittkampf et al 1989 and Yokoyama et al 2006). A major limitation of this catheter is the poor correlation of the tip temperature with the tissue temperature, often resulting in RF being curtailed and therefore incomplete lesions are made. The incidence of silent thromboembolic event in post ablation atrial fibrillation patients is 8.3% in irrigated tip catheter, 38.9% in duty cycled multielectrode catheter and 5.6% in cryoballoon (Gaita et al 2011). The duty cycled and cryoballoon ablation catheters

tissues.

**2.1 RF ablation non irrigated tip catheter** 

procedure using 8mm tip catheter. (Oral et al 2006)

**2.2 Irrigated tip electrode catheter** 

have further been explained in the chapter.

creation of larger lesions.

Fig. 1. Irrigated closed loop and open irrigation electrode catheter (Yokoyama et al 2006).

#### **3. Irrigated tip catheter with contact sensor**

RF ablation is dependent on good tissue contact where the ablation electrode is firmly embedded in the targeted tissue. The contact angle and the force between the tip of the catheter and the tissue surface play a major role in the characteristics of the lesion. Irrigated tip catheters with contact sensors can be used to estimate the contact force and angle (Figure 2). The catheter tip in this case is equipped with a deformable body that makes contact with the myocardial tissue. When subject to contact forces exerted by the tissue, the deformable body translates these forces into changes in wavelengths by optical fibers present within the catheter. Ultimately, these changes in wavelength are transformed via a computer algorithm to display both catheter vectors as well as contact force. The benefit of this catheter is that the combination of appropriate angle and force can be used to generate maximum transmurality with minimum incidence of steam pop and thrombus formation. (Schmidt et al 2009)

#### **4. Spiral catheter**

Another example of a catheter that is designed to specifically isolate the pulmonary vein (PV) Ostia resembles a corkscrew shape (Figure 3). This catheter is equipped with four 12 mm coil electrodes, with two thermistors placed at the edges of each coil to regulate the RF power, adjusting to the maximal sensed temperature from each thermistor (Avitall et al 2005). Standard radiofrequency generator with specialized interface was used.

The ablation catheter is introduced into the PVs via a 9F sheath. Once the tip of the catheter is in the PV, the sheath is withdrawn while maintaining the catheter position in the PV. As shown below, the spiral catheter expands within the vein and the coil electrodes are embedded within and under the orifice of the PV [figure 4]. Prior studies using this catheter demonstrated no visible PV narrowing during final PV angiography. PV circumferential lesions were documented in PVs and no PV stenosis was documented. One drawback however was the requirement to rotate the catheter position to create a circumferential lesion.

Past, Present and Future Catheter Technologies

et al 2009).

**5. The duty cycled multi electrode catheter** 

and Energy Sources for Atrial Fibrillation Ablation 191

The pulmonary vein ablation catheter (PVAC) or duty cycled multi electrode catheter (Ablation Frontiers, Inc., Carlsbad, CA, USA) is a 9F, over-the-wire, circumlinear (diameter 25mm), decapolar mapping and ablation catheter (Figure 5). The 3mm long platinum electrodes have an outer diameter of approximately 1.5mm and are spaced 3mm apart. Each electrode contains a thermocouple positioned on the surface contact side of the electrode. The catheter has 2 control handles. One allows bidirectional deflection of the shaft and the other is used to move the distal tip forward along the 0.032 mm guidewire, allowing a change of the catheter from its circular shape to a spiral configuration and finally to a longitudinal shape. The catheter is advanced through the sheath in its longitudinal shape and then deployed in the atria with the guidewire positioned in the vein (Boersma et al 2008). The GENius RF generator (Ablation Frontiers, Inc., Carlsbad, CA, USA) is a multichannel, dutycycled RF generator capable of independently delivering energy simultaneously to a maximum of 12 electrodes. RF energy can be delivered in unipolar (between ablation electrode and reference patch) and bipolar (between 2 adjacent ablation electrodes) configurations. Pairs of electrodes can be selected independently. During RF application, energy delivery is controlled by a software algorithm that modulates power to reach the user-defined target temperature (60C), but always limits power to a maximum of 10W per electrode. In this way, the ablation is "temperature controlled". Although this ablation technology limits the peak power to 10W, lower than with a non-irrigated 4 mm tip catheter, the current density applied at the tissue surface is approximately the same due to the smaller surface area of the electrodes. One limitation however is that achieving PV isolation requires rotation of the catheter to create overlapping circumferential lesions (Boersma et al 2008). Boersma et al studied 98 patients with paroxysmal or persistent AF to evaluate the feasibility and safety of this multielectrode catheter. All targeted PVs were isolated using this catheter, and follow-up after 6 months without antiarrhythmic drugs showed freedom from AF in 83% of patients. This study also demonstrated that fluoroscopy and procedural time appear to be shorter than those associated with current AF ablation techniques, without the need for sophisticated mapping and/or steering modalities (Wijffels

Fig. 5. PVAC (Decapolar Mapping and Ablation Catheter) (Wijffels et al.).

Fig. 2. Irrigated tip catheter with Contact sensor (Yokoyama et al 2008).

Fig. 3. PV ostia spiral catheter (Avitall et al 2005).

Fig. 4. Spiral catheter in Pulmonary veins, the spiral catheter expands within the vein and the coil electrodes are embedded within and under the orifice of the PV.

Fig. 4. Spiral catheter in Pulmonary veins, the spiral catheter expands within the vein and

the coil electrodes are embedded within and under the orifice of the PV.

Fig. 3. PV ostia spiral catheter (Avitall et al 2005).

.

Fig. 2. Irrigated tip catheter with Contact sensor (Yokoyama et al 2008).

#### **5. The duty cycled multi electrode catheter**

The pulmonary vein ablation catheter (PVAC) or duty cycled multi electrode catheter (Ablation Frontiers, Inc., Carlsbad, CA, USA) is a 9F, over-the-wire, circumlinear (diameter 25mm), decapolar mapping and ablation catheter (Figure 5). The 3mm long platinum electrodes have an outer diameter of approximately 1.5mm and are spaced 3mm apart. Each electrode contains a thermocouple positioned on the surface contact side of the electrode. The catheter has 2 control handles. One allows bidirectional deflection of the shaft and the other is used to move the distal tip forward along the 0.032 mm guidewire, allowing a change of the catheter from its circular shape to a spiral configuration and finally to a longitudinal shape. The catheter is advanced through the sheath in its longitudinal shape and then deployed in the atria with the guidewire positioned in the vein (Boersma et al 2008). The GENius RF generator (Ablation Frontiers, Inc., Carlsbad, CA, USA) is a multichannel, dutycycled RF generator capable of independently delivering energy simultaneously to a maximum of 12 electrodes. RF energy can be delivered in unipolar (between ablation electrode and reference patch) and bipolar (between 2 adjacent ablation electrodes) configurations. Pairs of electrodes can be selected independently. During RF application, energy delivery is controlled by a software algorithm that modulates power to reach the user-defined target temperature (60C), but always limits power to a maximum of 10W per electrode. In this way, the ablation is "temperature controlled". Although this ablation technology limits the peak power to 10W, lower than with a non-irrigated 4 mm tip catheter, the current density applied at the tissue surface is approximately the same due to the smaller surface area of the electrodes. One limitation however is that achieving PV isolation requires rotation of the catheter to create overlapping circumferential lesions (Boersma et al 2008). Boersma et al studied 98 patients with paroxysmal or persistent AF to evaluate the feasibility and safety of this multielectrode catheter. All targeted PVs were isolated using this catheter, and follow-up after 6 months without antiarrhythmic drugs showed freedom from AF in 83% of patients. This study also demonstrated that fluoroscopy and procedural time appear to be shorter than those associated with current AF ablation techniques, without the need for sophisticated mapping and/or steering modalities (Wijffels et al 2009).

Fig. 5. PVAC (Decapolar Mapping and Ablation Catheter) (Wijffels et al.).

Past, Present and Future Catheter Technologies

endocardial disruption. (Littman et al 1993)

**7.1 Visually guided Laser balloon catheter** 

lesions together to achieve a continuous circumferential lesion set.

decreased risk creating PV stenosis.

al 2004).

**7. Laser AF ablation** 

and Energy Sources for Atrial Fibrillation Ablation 193

A laser is a device that emits light (electromagnetic radiation) through a process of optical amplification based on the stimulated emission of photons. Emitted laser light is notable for its high degree of spatial and temporal coherence, unattainable using other technologies. Since duration and intensity of a laser can be controlled, it penetrates the tissue and scatters after getting absorbed in the tissue. Photon energy causes the vibrational excited state of surrounding molecules. This leads to generation of heat resulting in lesion creation. Laser energy can create deeper lesions with less reliance on thermal diffusion and can reduce tissue vaporization and coagulum formation. Because of its focused nature, it minimizes the collateral atrial tissue damage (Littman et al 1993). Two types of laser namely, Nd- YAG and Diode laser have been used in clinical application. Between them Diode laser with a wavelength of 980 nm, can minimize

Identification of the left atrial-pulmonary vein junction remains challenging, and additionally, creating contiguous lesions in a point by point manner to isolate the pulmonary veins (PV) is quite difficult. Balloon catheters provide an advantage in overcoming the challenge of charring and clot formation allowing for more precise lesion creation (Reddy et al 2004). The visually guided balloon catheter (Figure 7a) has an optic fiber head at the proximal end of the balloon and is equipped with an endoscope, permitting a visual angle of 110 degrees. When adequate tissue contact is made, tissue blanching will occur. If there is poor contact, however, then only free flowing blood is seen through the endoscope. Once the PV ostium is visualized, the next step is to use the optical fiber to target the laser arc at the appropriate tissue site. Correct identification of the ostium is critical to prevent formation of thrombus, which occurs when laser energy is focused on red blood cells. Keeping this in mind, the difference in the color of the light reflected is observed (seen as an arc) by the tissue and blood allows for assessment of contact. A red arc reflects contact with both tissue and blood, while green arc (Figure 7b) reflects balloon contact with tissue representing the target of ablation using this balloon technology. Once the arc is appropriately positioned to target the tissue of interest, a continuous 980-nm arc of laser energy is delivered. To avoid the overheating of myocardial tissue, sterile cooling fluid is circulated inside the balloon. Multiple arcs of ablation are applied to "stitch" individual

Studies utilizing visually guided balloon catheter ablation demonstrated long-term freedom from recurrence of atrial fibrillation at 67%, a rate comparable to that achieved with radiofrequency ablation (Reddy et al 2004**).** The delivery of deeper ablation energies in the pulmonary vein results in an increased risk of PV stenosis. The interface of the laser balloon catheter remains well outside the PV with the arc is projected on the ostium resulting in a

To prevent esophageal injury intraoperative temperature monitoring of the esophagus is done. If the temperature rises then the arc is either advanced or retracted.In addition there is less incidence of pericardial tamponade because of the controlled energy delivery. (Reddy et

#### **6. Loop catheter**

The loop catheter design for the creation of linear lesions in an effort to ablate AF was introduced in 1997. There are two main loop catheter systems, mostly used for experimental studies (Boston Scientific, EP Technologies, Sunnyvale, CA, USA) (Avitall et al 1999). Both catheter designs are shown in Figure 6. The first catheter system has twenty four 4mm ring electrodes that can create loops in the atria. In an effort to increase the efficiency of the ablation system, the second loop catheter was designed with fourteen 12-mm long coil electrodes 2 mm apart, equipped with two thermistors that were positioned at the two edges of each coil. The power is regulated to the maximal temperature measured between the two thermistors. Depending on the magnitude of the pullwire retraction and the size of the catheter portion extending from the sheath, the electrode portion of the catheter can form loops of various sizes. The body of the catheter applies pressure on the thin atrial walls and forces them to stretch around the catheter, maintaining consistent electrode–tissue contact along the entire length of the ablation portion of the catheter. Since the forces that are applied to the atrial walls are distributed along the catheter shaft around the loop, it is presumed that no single point is exposed to excessive forces. A locking mechanism holds the catheter and pullwire firmly in position. (Avitall et al 2002).

The most important determinant in the effective creation of a RF lesion is the electrode– tissue contact. Using the variable loop concept, the globular shaped atrial chambers will adapt around the catheter providing continuous contact. When using temperature control with this technology, over 90% of the lesions created in both atria were both contiguous and transmural while minimizing the incidence of significant rises in impedance. The catheter can be used to create linear lesions 6 mm wide and up to 16 cm long with minimal manipulation. Linear lesions were made by ablating at individual electrodes. Having multiple ablation electrodes on a single shaft allows for minimal catheter manipulation in creating long linear lesions and, therefore, may reduce both thromboembolic risk and radiation exposure. Once the catheter is in place, it remains in position for the duration of the power application to all of the electrodes (Avitall et al 2002).

Fig. 6. The loop catheter system. (A) 8F with 24 4-mm-long ring electrodes spaced 4 mm apart. (B) 8F with 14 12-mm-long coil electrodes spaced 2-mm apart. A soft, braided pull wire attached to the distal tip of the catheter can be retracted into the long guiding sheath to deflect the catheter tip to create a loop of various sizes. (Avitall et al 1999).

#### **7. Laser AF ablation**

192 Electrophysiology – From Plants to Heart

The loop catheter design for the creation of linear lesions in an effort to ablate AF was introduced in 1997. There are two main loop catheter systems, mostly used for experimental studies (Boston Scientific, EP Technologies, Sunnyvale, CA, USA) (Avitall et al 1999). Both catheter designs are shown in Figure 6. The first catheter system has twenty four 4mm ring electrodes that can create loops in the atria. In an effort to increase the efficiency of the ablation system, the second loop catheter was designed with fourteen 12-mm long coil electrodes 2 mm apart, equipped with two thermistors that were positioned at the two edges of each coil. The power is regulated to the maximal temperature measured between the two thermistors. Depending on the magnitude of the pullwire retraction and the size of the catheter portion extending from the sheath, the electrode portion of the catheter can form loops of various sizes. The body of the catheter applies pressure on the thin atrial walls and forces them to stretch around the catheter, maintaining consistent electrode–tissue contact along the entire length of the ablation portion of the catheter. Since the forces that are applied to the atrial walls are distributed along the catheter shaft around the loop, it is presumed that no single point is exposed to excessive forces. A locking mechanism holds

The most important determinant in the effective creation of a RF lesion is the electrode– tissue contact. Using the variable loop concept, the globular shaped atrial chambers will adapt around the catheter providing continuous contact. When using temperature control with this technology, over 90% of the lesions created in both atria were both contiguous and transmural while minimizing the incidence of significant rises in impedance. The catheter can be used to create linear lesions 6 mm wide and up to 16 cm long with minimal manipulation. Linear lesions were made by ablating at individual electrodes. Having multiple ablation electrodes on a single shaft allows for minimal catheter manipulation in creating long linear lesions and, therefore, may reduce both thromboembolic risk and radiation exposure. Once the catheter is in place, it remains in position for the duration of

Fig. 6. The loop catheter system. (A) 8F with 24 4-mm-long ring electrodes spaced 4 mm apart. (B) 8F with 14 12-mm-long coil electrodes spaced 2-mm apart. A soft, braided pull wire attached to the distal tip of the catheter can be retracted into the long guiding sheath to

deflect the catheter tip to create a loop of various sizes. (Avitall et al 1999).

the catheter and pullwire firmly in position. (Avitall et al 2002).

the power application to all of the electrodes (Avitall et al 2002).

**6. Loop catheter** 

A laser is a device that emits light (electromagnetic radiation) through a process of optical amplification based on the stimulated emission of photons. Emitted laser light is notable for its high degree of spatial and temporal coherence, unattainable using other technologies. Since duration and intensity of a laser can be controlled, it penetrates the tissue and scatters after getting absorbed in the tissue. Photon energy causes the vibrational excited state of surrounding molecules. This leads to generation of heat resulting in lesion creation. Laser energy can create deeper lesions with less reliance on thermal diffusion and can reduce tissue vaporization and coagulum formation. Because of its focused nature, it minimizes the collateral atrial tissue damage (Littman et al 1993). Two types of laser namely, Nd- YAG and Diode laser have been used in clinical application. Between them Diode laser with a wavelength of 980 nm, can minimize endocardial disruption. (Littman et al 1993)

#### **7.1 Visually guided Laser balloon catheter**

Identification of the left atrial-pulmonary vein junction remains challenging, and additionally, creating contiguous lesions in a point by point manner to isolate the pulmonary veins (PV) is quite difficult. Balloon catheters provide an advantage in overcoming the challenge of charring and clot formation allowing for more precise lesion creation (Reddy et al 2004). The visually guided balloon catheter (Figure 7a) has an optic fiber head at the proximal end of the balloon and is equipped with an endoscope, permitting a visual angle of 110 degrees. When adequate tissue contact is made, tissue blanching will occur. If there is poor contact, however, then only free flowing blood is seen through the endoscope. Once the PV ostium is visualized, the next step is to use the optical fiber to target the laser arc at the appropriate tissue site. Correct identification of the ostium is critical to prevent formation of thrombus, which occurs when laser energy is focused on red blood cells. Keeping this in mind, the difference in the color of the light reflected is observed (seen as an arc) by the tissue and blood allows for assessment of contact. A red arc reflects contact with both tissue and blood, while green arc (Figure 7b) reflects balloon contact with tissue representing the target of ablation using this balloon technology. Once the arc is appropriately positioned to target the tissue of interest, a continuous 980-nm arc of laser energy is delivered. To avoid the overheating of myocardial tissue, sterile cooling fluid is circulated inside the balloon. Multiple arcs of ablation are applied to "stitch" individual lesions together to achieve a continuous circumferential lesion set.

Studies utilizing visually guided balloon catheter ablation demonstrated long-term freedom from recurrence of atrial fibrillation at 67%, a rate comparable to that achieved with radiofrequency ablation (Reddy et al 2004**).** The delivery of deeper ablation energies in the pulmonary vein results in an increased risk of PV stenosis. The interface of the laser balloon catheter remains well outside the PV with the arc is projected on the ostium resulting in a decreased risk creating PV stenosis.

To prevent esophageal injury intraoperative temperature monitoring of the esophagus is done. If the temperature rises then the arc is either advanced or retracted.In addition there is less incidence of pericardial tamponade because of the controlled energy delivery. (Reddy et al 2004).

Past, Present and Future Catheter Technologies

of phrenic nerve or distal pulmonary veins.

inferior PV. (Reddy et al 2004).

**9. Cryothermal energy** 

and Energy Sources for Atrial Fibrillation Ablation 195

The balloon technology allows complete, 360° delivery of circumferential energy around the PV orifice, which may simplify the procedure. The balloon catheter has a predictable focused zone with very rapid achievement of lethal tissue temperatures. Power titration may control energy delivery and limit its impact on collateral tissue. This also highlights the need for careful monitoring of device positioning within the context of the geometry of the vein and adjacent structures. Use of balloons larger than the PV orifice may prevent injury

 Fig. 8 A. High-intensity focused ultrasound balloon ablation system. B: An ICE catheter is placed within the coronary to visualize the HIFU catheter positioned at the ostium of the left

Cryotechnology has been used for cardiac ablation for three decades, but catheter based ablation has been a more recent development. Cryothermal energy produces lesions through hypothermic exposure, which is a very different mechanism of tissue injury as compared to heat ablation. Cryolesions are generated by application of a cryoprobe cooled

Progressive cooling of cardiac tissue slows down conduction and eventually blocks electrical activity when temperatures are reduced to 0 to -20°C. Permanent lesions are

Applying the cryoprobe to the tissue surface causes the formation of a hemisphere of frozen tissue, or iceball. Ice crystals formed are seen both intracellularly and extracellularly. The primary mechanism of cell death is fatal structural change in subcellular organelles and the mitochondrial membrane. The electron transport system, which normally utilizes the mitochondrial membrane, stops working, this leads to irreversible mitochondrial damage, and ultimately cell death characterized by coagulative necrosis. Extracellular ice causes additional compression and distortion of adjacent cytoplasmic components and nuclei.

Histpathologically RF lesions cause complete disruption of elastic fibers in comparison to normal appearing elastic fibers in cryolesions. Esophageal injury can occur in both RF and cryo, however cryo tissue injury is often benign and reversible. RF is compared with

with liquid nitrous oxide for 2 – 5 minutes (Stobie et al 2003).

created when temperatures are reduced to -60 to -80 °C (Becker et al 2004).

Fig. 7a. Panel A visually guided balloon catheter displaying the green laser arc. In panel B Distal end of the catheter is shown. Catheter shaft endoscope and arc generator can be seen. (Reddy et al 2008).

Fig. 7b. In this figure, the arc of laser can be seen. The green light signifies the tissue and red light signifies the blood in the vein.

#### **8. High intensity focused ultrasound balloon system**

The High intensity focused ultrasound balloon system (HIFU) is a dual balloon in balloon design (Figure 8). The steerable HIFU catheter, a 10F catheter equipped with a 24mm diameter balloon, is advanced over the guidewire to the PV orifice, assisted by fluoroscopy and phased array intracardiac ultrasound (ICE) guidance. The anterior balloon is filled with fluid and the posterior with carbon dioxide. The interface created by the fluid and gas becomes the reflective interface of the ultrasound waves. The radially directed ultrasound energy is reflected forward to create a circumferential zone of concentrated ablative energy just beyond the face of the balloon. The mechanism of lesion formation is based on the conversion of the high intensity focused acoustic energy which causes molecular vibration that releases thermal energy in cardiac tissue. The steep tissue temperature gradient (2-5 °C per second) reaches 65-100°C with little heating of the adjacent tissue. (Okumura et al 2008 and Kennedy et al 2003)

Fig. 7a. Panel A visually guided balloon catheter displaying the green laser arc. In panel B Distal end of the catheter is shown. Catheter shaft endoscope and arc generator can be seen.

Fig. 7b. In this figure, the arc of laser can be seen. The green light signifies the tissue and red

The High intensity focused ultrasound balloon system (HIFU) is a dual balloon in balloon design (Figure 8). The steerable HIFU catheter, a 10F catheter equipped with a 24mm diameter balloon, is advanced over the guidewire to the PV orifice, assisted by fluoroscopy and phased array intracardiac ultrasound (ICE) guidance. The anterior balloon is filled with fluid and the posterior with carbon dioxide. The interface created by the fluid and gas becomes the reflective interface of the ultrasound waves. The radially directed ultrasound energy is reflected forward to create a circumferential zone of concentrated ablative energy just beyond the face of the balloon. The mechanism of lesion formation is based on the conversion of the high intensity focused acoustic energy which causes molecular vibration that releases thermal energy in cardiac tissue. The steep tissue temperature gradient (2-5 °C per second) reaches 65-100°C with little heating of the

(Reddy et al 2008).

light signifies the blood in the vein.

**8. High intensity focused ultrasound balloon system** 

adjacent tissue. (Okumura et al 2008 and Kennedy et al 2003)

The balloon technology allows complete, 360° delivery of circumferential energy around the PV orifice, which may simplify the procedure. The balloon catheter has a predictable focused zone with very rapid achievement of lethal tissue temperatures. Power titration may control energy delivery and limit its impact on collateral tissue. This also highlights the need for careful monitoring of device positioning within the context of the geometry of the vein and adjacent structures. Use of balloons larger than the PV orifice may prevent injury of phrenic nerve or distal pulmonary veins.

Fig. 8 A. High-intensity focused ultrasound balloon ablation system. B: An ICE catheter is placed within the coronary to visualize the HIFU catheter positioned at the ostium of the left inferior PV. (Reddy et al 2004).

#### **9. Cryothermal energy**

Cryotechnology has been used for cardiac ablation for three decades, but catheter based ablation has been a more recent development. Cryothermal energy produces lesions through hypothermic exposure, which is a very different mechanism of tissue injury as compared to heat ablation. Cryolesions are generated by application of a cryoprobe cooled with liquid nitrous oxide for 2 – 5 minutes (Stobie et al 2003).

Progressive cooling of cardiac tissue slows down conduction and eventually blocks electrical activity when temperatures are reduced to 0 to -20°C. Permanent lesions are created when temperatures are reduced to -60 to -80 °C (Becker et al 2004).

Applying the cryoprobe to the tissue surface causes the formation of a hemisphere of frozen tissue, or iceball. Ice crystals formed are seen both intracellularly and extracellularly. The primary mechanism of cell death is fatal structural change in subcellular organelles and the mitochondrial membrane. The electron transport system, which normally utilizes the mitochondrial membrane, stops working, this leads to irreversible mitochondrial damage, and ultimately cell death characterized by coagulative necrosis. Extracellular ice causes additional compression and distortion of adjacent cytoplasmic components and nuclei.

Histpathologically RF lesions cause complete disruption of elastic fibers in comparison to normal appearing elastic fibers in cryolesions. Esophageal injury can occur in both RF and cryo, however cryo tissue injury is often benign and reversible. RF is compared with

Past, Present and Future Catheter Technologies

Fig. 9. Cryoballoon.

(Ahmed et al 2010).

A B

(Ahmed et al 2011).

and Energy Sources for Atrial Fibrillation Ablation 197

Additionally, ablation time can be controlled by visualizing blanching at the site where ablation is taking place, which is indicative of lesion formation (Figure 10 and 11). This catheter is constantly irrigated to evacuate the blood collection in the hood to increase the visibility of the tissue and also to cool the tip. Increased power leads to bubble formation in the hood and darkening of the tissue. Such lesions often result in steam pop. As a result, bubble formation and darkening of the tissue could be an indicator for lowering the power

Fig. 10. Panel A: Visual field as seen through the endoscope. Pre ablation tissue is all red. Panel B: Post ablation tissue is pale as seen by the endoscopic visual field. \* shows the previous ablation lesion with panel B demonstrating visualization of lesion contiguity

Cryoablation in the table 2 below. Moreover, tensile strength of the tissue remains intact in cryolesions. The potential advantages of cryoablation over RF for ablation include a low risk of endocardial disruption, reduced incidence of thrombus formation, and stable adhesion of the catheter tip to the endocardium during freezing (Arora et al 2009).

#### **9.1 Cryoballoon**

New cryoballoon technology can safely and effectively electrically isolate the PVs (Avitall et al 2004). Avitall et al studied the original cryo balloon technology and found that after multiple consecutive cryolesions no PV stenosis was noted 3 months after ablation. After cryo ablation, PV electrograms were eliminated and tissue recovery exhibits no cartilage formation. Acute tissue hemorrhage and hemoptysis are short term complications of cryoablation. Arctic front cardiac cryoablation catheter developed by CryoCath is shown in the figure 9. It creates cryo lesions by delivering liquid N2O into the semi compliant balloon (23mm - 28mm diameter) and it is currently FDA approved for human PV isolation.


Table 1. Comparison of cryoablation vs radiofrequency ablation (Yiu et al 2006).

#### **10. Virtual electrode and visualization catheter**

In the Virtual and visual electrode catheter a unipolar tip electrode is present with an endoscope circumferential to the tip it has a hood made up of a flexible elastopolymer membrane at the proximal end. This hood carries the circumferential light source bands for illumination. Consequently, this catheter provides the means of directly visualizing the target tissue that needs to be ablated. It is helpful in maintaining the contiguity of the lesions and also decreases the total procedure time.

Cryoablation in the table 2 below. Moreover, tensile strength of the tissue remains intact in cryolesions. The potential advantages of cryoablation over RF for ablation include a low risk of endocardial disruption, reduced incidence of thrombus formation, and stable adhesion of

New cryoballoon technology can safely and effectively electrically isolate the PVs (Avitall et al 2004). Avitall et al studied the original cryo balloon technology and found that after multiple consecutive cryolesions no PV stenosis was noted 3 months after ablation. After cryo ablation, PV electrograms were eliminated and tissue recovery exhibits no cartilage formation. Acute tissue hemorrhage and hemoptysis are short term complications of cryoablation. Arctic front cardiac cryoablation catheter developed by CryoCath is shown in the figure 9. It creates cryo lesions by delivering liquid N2O into the semi compliant balloon (23mm - 28mm diameter) and it is currently FDA approved for human PV

Table 1. Comparison of cryoablation vs radiofrequency ablation (Yiu et al 2006).

In the Virtual and visual electrode catheter a unipolar tip electrode is present with an endoscope circumferential to the tip it has a hood made up of a flexible elastopolymer membrane at the proximal end. This hood carries the circumferential light source bands for illumination. Consequently, this catheter provides the means of directly visualizing the target tissue that needs to be ablated. It is helpful in maintaining the contiguity of the lesions

**10. Virtual electrode and visualization catheter** 

and also decreases the total procedure time.

the catheter tip to the endocardium during freezing (Arora et al 2009).

**9.1 Cryoballoon** 

isolation.

#### Fig. 9. Cryoballoon.

Additionally, ablation time can be controlled by visualizing blanching at the site where ablation is taking place, which is indicative of lesion formation (Figure 10 and 11). This catheter is constantly irrigated to evacuate the blood collection in the hood to increase the visibility of the tissue and also to cool the tip. Increased power leads to bubble formation in the hood and darkening of the tissue. Such lesions often result in steam pop. As a result, bubble formation and darkening of the tissue could be an indicator for lowering the power (Ahmed et al 2010).

Fig. 10. Panel A: Visual field as seen through the endoscope. Pre ablation tissue is all red. Panel B: Post ablation tissue is pale as seen by the endoscopic visual field. \* shows the previous ablation lesion with panel B demonstrating visualization of lesion contiguity (Ahmed et al 2011).

Past, Present and Future Catheter Technologies

**12. Conclusion** 

question.

**13. References** 

33(4):972-984.

and Energy Sources for Atrial Fibrillation Ablation 199

Table 2.Comparison of Radiofrequency ablation and microwave ablations (Yiu et al 2006).

To date, many patients with refractory supraventricular tachyarrythmias have been successfully ablated without complications, however successful ablation of atrial fibrillation continues to pose unique problems to the cardiac electrophysiologist. While progress has been made on identification of the triggers and underlying substrate of atrial fibrillation, the tools necessary to isolate and ablate AF lags behind our knowledge of the mechanisms underlying this arrhythmia. The ideal catheter should possess the best mapping resolution to target the tissues of interest, create reliable transmural and contiguous lesions, and clearly discriminate between successful and unsuccessful lesion formation and maturation. Furthermore, the ideal catheter technology should be easily steered and adapt to the atrial anatomy reducing the procedure time. Further benefits of such an approach would be decreasing excessive exposure of radiation to the physician and the patient in the EP lab. So far, balloon devices seem to offer a unique promise, however lesion transmurality is still a

Avitall B., Lafontaine D., Rozmus G., Adoni N., Le K., Dehnee A., Urbonas A.; The safety

Avitall B, Helms R, Koblish J, Seiben W, Kotov AV, Gupta GN. The creation of linear

atrial junction. Heart Rhythm, (2004) Volume 1, Issue 2, Pages 203 – 209. Avitall B., Urboniene D., Rozmus G., Lafontaine D., Helms R., and Urbonas A.; New

Electrophysiol (March 2003) Volume 14 Issue 3, Pages 281 – 286.

and efficacy of multiple consecutive cryo lesions in canine pulmonary veins-left

Cryotechnology for Electrical Isolation of the Pulmonary Veins. J Cardiovasc

contiguous lesions in the atria with an expandable loop catheter. JACC 1999;

Identified limitations of this catheter relate to technical difficulties of fixing the hood at the tissue interface, especially at rough surface of atrial tissue and edges around the pulmonary veins. The nature of the elastopolymer coating results in slippage of the catheter. It has also been seen to collapse, likely related to the force generated during lesion formation, requiring catheter replacement in certain cases (Ahmed et al 2011).

Fig. 11 A. Blue lines indicate the saline irrigation, purple lines indicate radiofrequency; Red lines indicate the flowing blood .B, C, D Virtual and visual electrode catheter from different angles. Hood with source of illumination can be seen clearly in panel C, endoscope and electrodes in the center are clearly visible in panel B. (Ahmed et al 2011).

Besides the technical limitations, current studies using this technology are limited by their small sample size, lack of application to atrial fibrillation and concerns over the volume of irrigation fluid delivered during the course of an ablation using this technology (Ahmed et al 2011)**.** 

#### **11. Microwave**

Microwave energy is an electromagnetic spectrum occupying the frequency range between 500 MHz – 100 MHz. When this electromagnetic radiation comes in contact with the biological tissues, it causes bipolar molecules (particularly water molecules) to oscillate and rotate under the influence of alternating electromagnetic radiation. This oscillation results in the conversion into kinetic energy, and finally collision of molecules cause heat energy formation (Johnson et al 1972). This (microwave induced) heat forms in deeper tissues as compared to RF where heat flows down the tissue interface to the deeper tissues via conductive heating, decreasing as a function of distance (1/r4). Microwave energy excites deeper tissues resulting in deep high temperature and larger lesions.

In fact, microwave induced scar seems to be the endpoint of two distinct pathways. The first pathway is the direct effect of microwave radiation, while the second is a result of ischemic damage.


Table 2.Comparison of Radiofrequency ablation and microwave ablations (Yiu et al 2006).

#### **12. Conclusion**

198 Electrophysiology – From Plants to Heart

Identified limitations of this catheter relate to technical difficulties of fixing the hood at the tissue interface, especially at rough surface of atrial tissue and edges around the pulmonary veins. The nature of the elastopolymer coating results in slippage of the catheter. It has also been seen to collapse, likely related to the force generated during lesion formation, requiring

Fig. 11 A. Blue lines indicate the saline irrigation, purple lines indicate radiofrequency; Red lines indicate the flowing blood .B, C, D Virtual and visual electrode catheter from different angles. Hood with source of illumination can be seen clearly in panel C, endoscope and

Besides the technical limitations, current studies using this technology are limited by their small sample size, lack of application to atrial fibrillation and concerns over the volume of irrigation fluid delivered during the course of an ablation using this technology (Ahmed et

Microwave energy is an electromagnetic spectrum occupying the frequency range between 500 MHz – 100 MHz. When this electromagnetic radiation comes in contact with the biological tissues, it causes bipolar molecules (particularly water molecules) to oscillate and rotate under the influence of alternating electromagnetic radiation. This oscillation results in the conversion into kinetic energy, and finally collision of molecules cause heat energy formation (Johnson et al 1972). This (microwave induced) heat forms in deeper tissues as compared to RF where heat flows down the tissue interface to the deeper tissues via conductive heating, decreasing as a function of distance (1/r4). Microwave energy excites

In fact, microwave induced scar seems to be the endpoint of two distinct pathways. The first pathway is the direct effect of microwave radiation, while the second is a result of ischemic

electrodes in the center are clearly visible in panel B. (Ahmed et al 2011).

deeper tissues resulting in deep high temperature and larger lesions.

al 2011)**.** 

damage.

**11. Microwave** 

catheter replacement in certain cases (Ahmed et al 2011).

To date, many patients with refractory supraventricular tachyarrythmias have been successfully ablated without complications, however successful ablation of atrial fibrillation continues to pose unique problems to the cardiac electrophysiologist. While progress has been made on identification of the triggers and underlying substrate of atrial fibrillation, the tools necessary to isolate and ablate AF lags behind our knowledge of the mechanisms underlying this arrhythmia. The ideal catheter should possess the best mapping resolution to target the tissues of interest, create reliable transmural and contiguous lesions, and clearly discriminate between successful and unsuccessful lesion formation and maturation. Furthermore, the ideal catheter technology should be easily steered and adapt to the atrial anatomy reducing the procedure time. Further benefits of such an approach would be decreasing excessive exposure of radiation to the physician and the patient in the EP lab. So far, balloon devices seem to offer a unique promise, however lesion transmurality is still a question.

#### **13. References**


Past, Present and Future Catheter Technologies

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### *Edited by Saeed Oraii*

The outstanding evolution of recording techniques paved the way for better understanding of electrophysiological phenomena within the human organs, including the cardiovascular, ophthalmologic and neural systems. In the field of cardiac electrophysiology, the development of more and more sophisticated recording and mapping techniques made it possible to elucidate the mechanism of various cardiac arrhythmias. This has even led to the evolution of techniques to ablate and cure most complex cardiac arrhythmias. Nevertheless, there is still a long way ahead and this book can be considered a valuable addition to the current knowledge in subjects related to bioelectricity from plants to the human heart.

Electrophysiology - From Plants to Heart

Electrophysiology

From Plants to Heart

*Edited by Saeed Oraii*

Photo by chaikom / iStock