Capacitive heating of phantom and human tumors with an 8 MHz radiofrequency applicator (Thermotron RF-8)

The thermal profile was investigated in agar phantoms and in human tumors heated capacitively with 8 MHz RF. Deep and homogeneous heating could be achieved in a large homogeneous phantom of 25 cm diameter and 24 cm thick when heated with a pair of 25 cm diameter electrodes, coupled to both bases of the phantom. When the size of the two electrodes was not the same, the region near the smaller electrode was preferentially heated. It was, therefore, possible to control the depth of heating by choosing properly sized electrodes. Therapeutic temperature (greater than 42 degrees C) could be obtained in 7 out of 9 small, as well as, bulky superficial human tumors as large as 8 X 8 X 10 cm. Indications are that heating of some deep-seated human tumors might be achieved by the capacitive method, provided that subcutaneous fat layer is cooled by temperature controlled bolus and large electrodes are used. The effect of the anatomical structure on the power deposition in the human body during capacitive heating should be further investigated.     

Deep-heating characteristics of an RF capacitive heating device

An RF capacitive heating device was constructed and its deep-heating characteristics were studied using three mini-pigs. The deep-heating ability of RF capacitive heating was found to be improved by enlarging the electrodes, driving at 8 MHz, cooling the skin under the electrodes, inserting a bolus between the body and the electrodes and considering the anatomical structure of the body. The heating characteristics obtained were as follows. When applicators were placed on both sides of the abdomen of a mini-pig, 7 mm in fat layer thickness and 23 cm in lateral chest thickness, the increase in temperature of the deep part was greater than that of the fat layer. When applicators were placed on the posterior and anterior abdomen, overheating was noted in the fat and muscle near the back. The temperature was highest in a mock tumour, made by blocking blood flow to the spleen. The bio-heat equation revealed that RF capacitive heating accompanied by surface cooling at 10 degrees C could heat the deep portion of the body to 42 degrees C without excessive heating of a 1.6 cm thick fat layer.     

Radiofrequency capacitive hyperthermia for deep-seated tumors. I. Studies on thermometry

The thermometry results of radiofrequency (RF) capacitive hyperthermia for 60 deep-seated tumors in 59 patients are reported. Hyperthermia was administered regionally using two RF capacitive heating equipments which the authors have developed in cooperation with Yamamoto Vinyter Company Ltd., (Osaka, Japan). Intratumor temperatures were measured by thermocouples inserted through angiocatheters which were placed 5 cm to 12 cm deep into the tissues. Tumor center temperatures were measured for 307 treatments in all tumors; thermal distributions within tumors and surrounding normal tissues were obtained for 266 treatments of 53 tumors by microthermocouples. Thermometry results obtained were summarized as follows. A maximum tumor center temperature greater than 43 degrees C and 42 degrees C to 43 degrees C was obtained in 23 (38%) and 14 (23%) of the 60 tumors respectively. The time required to reach 43 degrees C in the tumor center was within 20 minutes after the start of hyperthermia in 87% of tumors heated to more than 43 degrees C. Temperature variations within a tumor exceeded 2 degrees C in 81% of tumors heated to more than 43 degrees C. The lowest tumor temperature greater than 42 degrees C was achieved in six of the 53 tumors (11%). Of 42 tumors in which temperatures of the subcutaneous fat, surrounding normal tissues, and the tumor center were compared, 24 (57%) showed the highest temperature in the tumor center and ten (24%) in the subcutaneous fat. When the heating efficacy was assessed in terms of a maximum tumor center, it great deal depended on the treatment site, tumor size, thickness of subcutaneous fat, and tumor type. Tumors in the head and neck, thorax, lower abdomen, and pelvis could be heated better than tumors in the upper abdomen. Greater heating efficacy was shown in patients with large, hypovascular tumors, and with the subcutaneous fat measuring less than 15 mm thick. The predominant limiting factor for power elevation was pain associated with heating. Systemic signs including increases in pulse rate and body temperature were not serious and seldom became limiting factors for power elevation. Our thermometry results indicate that the advantages of deep RF capacitive heating are its applicability to various anatomic sites and negligible systemic effects. The disadvantages are that its primary usefulness is limited to patients with thin subcutaneous fat and with large or hypovascular tumors.     

Hyperthermia combined with radiation therapy for primarily unresectable and recurrent colorectal cancer.

The value of adjuvant hyperthermia to radiotherapy in the treatment of locally advanced colorectal cancers was investigated. Between 1981 and 1989, 71 primarily unresectable or recurrent colorectal tumors were treated with radiotherapy at the Department of Radiology, Kyoto University Hospital. Of the 71 tumors, 35 were treated with radiotherapy plus hyperthermia (group I), while 36 tumors (group II) were unsuitable for hyperthermia mainly because of difficulties with the insertion of temperature probes or the thickness of the patient's subcutaneous fat (greater than 2 cm). The mean total radiation dose was 58 Gy and 57 Gy for groups I and II, respectively. Thirty deep-seated pelvic tumors were treated with an 8 MHz radiofrequency capacitive heating device, and five subsurface tumors were treated with a 430 MHz microwave hyperthermia system. Hyperthermia was given following radiotherapy for 30-60 min for a total of 2-14 sessions (mean 5.7). In 32 of the 35 tumors heated, direct measurement of tumor temperature was performed. For the five tumors treated with the microwave heating device, the means of the mean maximum, average, and minimum measured intratumoral temperatures were 45.4 degrees C, 43.3 degrees C, and 40.6 degrees C, respectively. The corresponding values were 42.2 degrees C, 41.3 degrees C, and 40.3 degrees C for the 27 tumors treated with the capacitive heating device. Effective heating of deep-seated pelvic tumors was more difficult than heating of abdominal wall or perineal tumors. The local control rate at 6 months after the treatment, which was defined as absence of local progression of the tumors, was 59% (17/29) and 37% (11/30) for groups I and II, respectively. The objective tumor response rate (complete regression plus partial response) evaluated by computed tomography was 54% (19/35) in group I, whereas it was 36% (10/28) in group II. A better response rate of 67% was obtained in the 15 tumors with a mean average tumor temperature of greater than 42 degrees C. Although limitation of our current heating devices exist, the combination of hyperthermia with radiotherapy is a promising treatment modality in the treatment of locally advanced colorectal cancer.     

Radiofrequency capacitive heating of deep-seated tumours using pre-cooling of the subcutaneous tissues: results on thermometry in Dutch patients.

The capacity of a radiofrequency, 13.56 MHz, capacitive hyperthermia system using extensive pre-cooling of the subcutaneous tissue to induce locoregional deep heating has been investigated in 11 patients. Tumour location was presacral in nine--and eccentric towards the lateral side of the pelvis in two patients. For thermometry multiple catheters (mean 2.7) were inserted into the treatment volume. The mean numbers of temperature measuring points per treatment were 9.4 in tumour, 5.5 in muscle and 7.2 in subcutaneous fat. RF energy was applied after 30 min of cooling through two flexible boli perfused with saline water at 5-10 degrees C. Patient tolerance to pre-cooling was very good and after some initial discomfort the patient became rapidly accustomed to the cold water boli. For some patients better temperatures were achieved when the conventional anterior-posterior applicator set-up was replaced by a set-up with an applicator on each lateral side of the patient. As patients can tolerate temperatures within the fat tissue as high as 45.5 degrees C without complaining it appears important to monitor the temperature at the transition of fat to muscle tissue to prevent subcutaneous burns. The study shows that pre-cooling cannot avoid preferential heating at the interface from fat to muscle tissue. In this patient group the quality of the hyperthermia treatment appeared to be rather poor: 60% of the measured tumour temperatures were below 40 degrees D.     

A comparison of the heating characteristics of capacitive and radiative superficial hyperthermia

Background: Superficial hyperthermia is applied in combination with radiotherapy for e.g. melanoma and recurrent breast cancer, using both capacitive and radiative systems. In this paper, numerical simulations are applied to address the question which technique yields the most favourable heating characteristics.

Methods: A 434?MHz contact flexible microstrip applicator (CFMA type 4H, size 19.6?×?19.6?cm²) and a capacitive system consisting of two circular electrodes with diameter 15 and 25?cm were modelled. The water bolus of the CFMA was filled with deionised water and for capacitive heating both saline and deionised water were modelled. Specific absorption rate (SAR) and temperature simulations were performed for a perfused muscle-equivalent phantom and phantoms with a 1?cm thick superficial fat layer, assuming cylindrical target regions. Subsequently, a real patient model with a chest wall recurrence was studied with the target assumed to have muscle-like properties, fat properties or heterogeneous properties as derived from the CT Hounsfield Units.

Results: Phantom simulations showed that high SAR peaks occur around the bolus edges with capacitive heating. Power absorption below the fat layer is substantially higher for radiative heating and unless the target region is limited to the fat layer, radiative heating yields better target coverage in terms of SAR and temperature. Patient simulations showed that the T₉₀ for radiative heating was 0.4–1.1?°C higher compared with capacitive heating.

Conclusions: Radiative heating yields more favourable SAR and temperature distributions for superficial tumours, compared with capacitive heating, especially within heterogeneous tissues. Higher tumour temperatures are achieved without occurrence of treatment limiting hot spots.     

Clinical evaluation of hyperthermia with radiofrequency capacitive heating in combination with radiotherapy

Clinical studies of radiofrequency (RF) hyperthermia combined with radiotherapy have been applied on the superficial bulky tumors and deep-seated tumors. Some improvement during the local heating was achieved by applying the small pad and/or the overlay bolus onto the skin surface underlain by subcutaneous fatty tissue. The condition of effective heating on tumors had shown to have a tendency to lead a good response regarding reduction rates in a tumor size. However, for the clinical evaluation, we have considered that it should be suitable to apply such findings as one showing the necrotic degenerative changes on computed tomograms in addition to the evaluation guide on the local response.     

Locoregional hyperthermia of deep-seated tumours applied with capacitive and radiative systems: a simulation study

Background: Locoregional hyperthermia is applied to deep-seated tumours in the pelvic region. Two very different heating techniques are often applied: capacitive and radiative heating. In this paper, numerical simulations are applied to compare the performance of both techniques in heating of deep-seated tumours.

Methods: Phantom simulations were performed for small (30?×?20?×?50?cm³) and large (45?×?30?×?50?cm³), homogeneous fatless and inhomogeneous fat-muscle, tissue-equivalent phantoms with a central or eccentric target region. Radiative heating was simulated with the 70?MHz AMC-4 system and capacitive heating was simulated at 13.56?MHz. Simulations were performed for small fatless, small (i.e. fat layer typically <2?cm) and large (i.e. fat layer typically >3?cm) patients with cervix, prostate, bladder and rectum cancer. Temperature distributions were simulated using constant hyperthermic-level perfusion values with tissue constraints of 44?°C and compared for both heating techniques.

Results: For the small homogeneous phantom, similar target heating was predicted with radiative and capacitive heating. For the large homogeneous phantom, most effective target heating was predicted with capacitive heating. For inhomogeneous phantoms, hot spots in the fat layer limit adequate capacitive heating, and simulated target temperatures with radiative heating were 2–4?°C higher. Patient simulations predicted therapeutic target temperatures with capacitive heating for fatless patients, but radiative heating was more robust for all tumour sites and patient sizes, yielding target temperatures 1–3?°C higher than those predicted for capacitive heating.

Conclusion: Generally, radiative locoregional heating yields more favourable simulated temperature distributions for deep-seated pelvic tumours, compared with capacitive heating. Therapeutic temperatures are predicted for capacitive heating in patients with (almost) no fat.     

Magnetic induction heating of tissue: numerical evaluation of tumor temperature distributions

A one dimensional (radial) numerical model based on the bioheat transfer equation has been developed and applied to the abdomen and pelvis heated by a concentric magnetic induction electrode. This model consists of four normal tissue regions: viscera, muscle, fat and skin. Each region is assigned thermal properties characteristic of that region and power deposition values consistent with those for this mode of heating. Tumors of 2, 4 and 7 cm thicknesses are positioned in five different radial locations ranging from the central axis to the skin surface. Two blood perfusion models of the tumor are considered: the uniformly perfused model and an annular model. Tumor temperature distributions are considered acceptable if the average tumor temperature plus and minus two standard deviations lie between 42 degrees C and 60 degrees C. To stimulate practical clinical restrictions, muscle and fat temperatures are not allowed to exceed 44 degrees C, significant portions of the viscera (except for a 1 cm thick band) are not allowed to exceed 42 degrees C, and the total absorbed power required to maintain steady state cannot exceed one kilowatt. Over 100 possible cases are presented in a compact form. A conclusion drawn from this study is that with few exceptions, only small tumors in the muscle annulus are heated adequately with this modality. Large tumors will have significant unheated portions if the specified limitations are not exceeded. While this heating modality can raise the necrotic core of a tumor to high temperatures, it cannot adequately heat well perfused regions of a deep seated tumor. These conclusions are borne out clinically and are discussed in a companion paper.     

A practical system for clinical radiofrequency hyperthermia

This paper describes an apparatus for inducing local hyperthermis by passing high-frequency electrical currents through tissues between electrodes placed against the skin of the patient. The electrodes use a temperature-controlled saline solution contained by a thin rubber membrane to make contact. The resistivity of the saline solution is matched to that of body tissues. This yields a smooth transition from electrode to tissue, thereby greatly reducing the possibility of producing the skin burns which frequently appear along the edges of metallic electrodes. Use of the thin rubber membrane allows easy molding of a given set of electrodes to complex body contours for many different patients. The equipment has proven capable in clinical tests of heating bulky tumors in the head and neck and extremities without significant skin toxicity. Excessive beating of the subcutaneous fat, however, restricts the application of this heating method to tumors located in areas of the body with sparse adipose tissue.     

Radiofrequency capacitive heating of deep-seated tumours using pre-cooling of the subcutaneous tissues: Results on thermometry in Dutch patients

The capability of a radiofrequency, 13.56 MHz, capacitive hyperthermia system using extensive pre-cooling of the subcutaneous tissue to induce locoregional deep heating has been investigated in 11 patients. Tumour location was presacral in nine—and eccentric towards the lateral side of the pelvis in two patients. For thermometry multiple catheters (mean 2.7) were inserted into the treatment volume. The mean numbers of temperature measuring points per treatment were 9.4 in tumour, 5.5 in muscle and 7.2 in subcutaneous fat. RF energy was applied after 30 min of cooling through two flexible boli perfused with saline water at 5–10°. Patient tolerance to pre-cooling was very good and after some initial discomfort the patient became rapidly accustomed to the cold water boli. For some patients better temperatures were achieved when the conventional anterior-posterior applicator set-up was replaced by a set-up with an applicator on each lateral side of the patient. As patients can tolerate temperatures within the fat tissue as high as 45.5° without complaining it appears important to monitor the temperature at the transition of fat to muscle tissue to prevent subcutaneous burns. The study shows that pre-cooling cannot avoid preferential heating at the interface from fat to muscle tissue. In this patient group the quality of the hyperthermia treatment appeared to be rather poor: 60% of the measured tumour temperatures were below 40°.     

Clinical results of radiofrequency capacitive hyperthermia in deep-seated tumors

The advantages of deep radiofrequency (RF) capacitive heating are its applicability to various anatomical sites and negligible systemic effects. The disadvantages are on the other hand, that its primary usefulness is limited to patients with thin subcutaneous fat and with large or hypovascular tumors. Clinical benefits of RF hyperthermia combined with radiotherapy are strongly suggested for deep-seated tumors. Intratumor low density areas on post-treatment CT and histopathological examinations are considered important parameters to assess the tumor response to thermoradiotherapy.     

Local RF capacitive hyperthermia: thermal profiles and tumour response

At the Cancer Institute we are using RF capacitive hyperthermia as an adjuvant to radiotherapy and/or chemotherapy in the local control of soft tissue sarcomas. We have studied the influence of bolus conductivity, electrode and phantom sizes on the rate of heating of agar phantoms. We have varied the bolus conductivity by varying the saline concentration in the bolus bags from zero to 2.0 per cent, during heating. We found that the rate of heating of phantoms increases and that of the bolus decreases with the increase in the saline concentration of bolus up to 1 per cent, irrespective of phantom and electrode sizes. However, for a given size of electrodes the rate of heating decreased with the increase in the phantom size. When the diameter and height of the phantom were equal to the diameters of electrodes the rate of heating of the phantom was nearly uniform. However, when the diameter of the phantom was larger than that of electrodes the rate of heating in the radial axis decreased with the increase in the radial distance. On the basis of this data we suggest the use of electrodes larger in size by 1.0-3.0 cm than the size of the tumour, where the size of the anatomical site to be heated is larger than the electrode size to be used. Phantom and clinical data have indicated that the presence of bone in the field of heating can lead to hot spots. Preliminary clinical results have shown that the response of sarcomas to thermo-chemo-radiotherapy was superior to that of either thermo-radiotherapy or radiotherapy alone.     

Effect of 8-MHz radiofrequency-capacitive regional hyperthermia with strong superficial cooling for unresectable or recurrent colorectal cancer.

A well-known disadvantage of a radiofrequency-capacitive device for deep-seated tumours is preferential heating of the subcutaneous fat tissue. The authors previously developed the hyperthermia with their own external cooling unit and achieved strong superficial cooling, and reported its usefulness for the reduction of the preferential heating. The purpose of the present study was to evaluate the effect of hyperthermia with strong superficial cooling on the treatment results for unresectable or recurrent colorectal cancers. From 1986 to 2002, 44 patients with primary unresectable or locally recurrent colorectal cancer treated with thermoradiotherapy were analysed retrospectively. The patients with obesity as a subcutaneous fat thickness more than 3 cm, a high age or other serious complications did not undergo therapy. The results were compared between 17 cases with strong superficial cooling treated after 1997 (Group A) and 27 cases without strong superficial cooling treated before 1996 (Group B). Significant differences in thermometry data of T(max), T(ave) and T(min) were noted between Groups A (45.3, 44.4 and 43.6 degrees C, respectively) and B (42.9, 42.0 and 41.1 degrees C, respectively) (p<0.01). Complete response plus partial response rates were better for Group A than for Group B (59 versus 26%, p = 0.05). Multivariate analysis by logistic regression to evaluate the effects of certain factors on complete response plus partial response was strongly correlated with strong superficial cooling (p<0.05). The median survival times for overall survival were 24.3 months for Group A and 17.1 months for Group B (p<0.05). Eight-megahertz radiofrequency-capacitive regional hyperthermia with strong superficial cooling is potentially useful for improving treatment results in unresectable or recurrent colorectal cancers.     

Hyperthermia with implanted electrodes: in vitro and in vivo correlations

Hyperthermia as a treatment for cancer has elicited much recent interest. However, major difficulties persist both in the technology for heating deep-seated tumors, and in thermal dosimetry. We have investigated a heating technique for deep-seated neoplasms that employs an internal implanted electrode and an external electrode to apply radiofrequency current to a tumor mass. The internal electrode consists of an array of stainless steel needles or wires which define a Faraday cage within the tumor, while the external electrode consists of a variety of electrical conductors at the skin surface. Phantom measurements have closely reproduced calculated temperature distributions. The temperature profiles within the volume enclosed by the internal electrode show relatively homogenous heating. Temperature measurements in a rat tumor model have demonstrated that significant heating within such an internal electrode array is easily obtained. The heating may extend some centimeters outside the electrode. Using a dog model we have shown that with such a treatment technique the temperature profiles obtained are reproducible both spatially and temporally. A case report of a clinical application is presented. A 5 cm bronchogenic carcinoma was easily heated without significant heating of the surrounding normal lung, and without apparent toxicity. Such a technique may be applicable to a variety of operable but unresectable neoplasms. The reproducibility and relative homogeneity of heating suggest possible usefulness in combined modality trials.     

Effects of fat thickness on heating patterns of the microwave applicator MA-151 at 631 and 915 MHz

Previous studies showed that the surface heating patterns of the MA-151 applicator on a 2 cm fat and 10 cm thick muscle phantom had center heating at 581 and 930 MHz and two hot spots near the edges of the applicator at 657 and 779 MHz. The hot spots at 657 MHz were consistent with two blisters on a patient's thigh. Since the heating patterns on muscle only showed good center elliptical heating at all frequencies, in this study we have investigated the effects of fat thickness on the heating patterns. Thermograms of fat and muscle surfaces were taken on phantoms with 0, 0.25, 0.5, 1, and 2 cm thick fat exposed to 631 or 915 MHz energy. The 631 MHz was selected to provide reasonable energy coupling for all phantoms. At 631 MHz, two hot spots were evident on all fat surfaces. The pattern on the muscle surface under the 0.25 cm fat did not show two hot spots, but the heating was elongated in the E-field direction. At 915 MHz, the heating was elongated on the surface of the 0.25 and 2 cm fat, and two hot spots were observed on the 0.5 and 1 cm fat surfaces. However, the muscle heating was elliptical in all cases. The ratio of muscle to fat heating decreased as the fat thickness increased. At 0.5 cm fat the ratio was about 1. These results indicate that fat thickness influences heating in muscle. During treatment with this applicator, surface temperature probes should be placed over potential hot spots. Surface cooling is desirable for heating tumors beneath the fat.     

Radiofrequency capacitive hyperthermia for deep-seated tumors. II. Effects of thermoradiotherapy

Clinical effects and safety of radiofrequency (RF) capacitive hyperthermia in combination with radiotherapy were evaluated in 40 patients with locally advanced deep-seated tumors. Hyperthermia was administered regionally with an 8-MHz or a 13.56-MHz RF heating device, once or twice a week after irradiation, four to 13 sessions total. Radiotherapy was delivered in fractions of 170 to 200 cGy a day, 5 days a week to 30 to 70 Gy to 33 patients, whereas the remaining seven patients received a total dose of 28 to 60 Gy in fractions of 400 cGy, twice a week. Six of the 40 tumors treated showed CR (100% regression), 6 PRa (80%-100% regression), 13 PRb (50%-80% regression), and 15 NR (less than 50% regression) when assessed by tumor size on computerized tomography (CT) scan. The tumor size before treatment was significantly smaller in CR + PRa tumors than in PRb + NR ones. TDF Time-dose fractionation (TDF) and number of heat treatments, however, did not differ significantly between the both tumors. Greater regression was observed in tumors heated to 41 to 43 degrees C in the maximum temperature than in tumors heated to below 41 degrees C or above 43 degrees C. The minimum tumor temperature was not related to the tumor regression. Posttreatment CT scan revealed remarkable low-density areas in 18 of the 34 tumors that did not regress completely. Histopathologic examinations demonstrated the low-density area to be massive coagulation necrosis and no malignant cell was observed in two tumors examined thoroughly. The types of low-density areas, which were classified according to its percent area in the tumor, correlated with the maximum and minimum tumor temperature. Most of the type III tumors (more than 80% low density) did not regrow in follow-up studies. Complications consisted of subcutaneous fat necrosis in four patients, local edema in four patients, and one abdominal abscess in one patient, all of which eventually resolved. These clinical results strongly suggest the usefulness of RF capacitive hyperthermia combined with radiotherapy for the treatment of refractory deep-seated tumors, and that intratumor low-density areas which appear on posttreatment CT seems to be a good parameter for assessing the tumor response to thermoradiotherapy.     

Heating efficiency of radiofrequency capacitive hyperthermia for treatment of deep-seated tumors in the peritoneal cavity

We analyzed heating profiles from 318 hyperthermic treatments of 39 patients with recurrent or inoperable cancers of the digestive organs whose deep-seated tumors were treated by radiofrequency (RF) capacitive heating of the abdominal region, and we investigated the heating efficiency and antitumor effect of such treatment. It was apparent that heating with a mean maximum RF output of 1,000 watts (700 watts at least), repeated four times or more, was necessary for a high rate of response by the tumor. Although it was difficult to heat tumors of the bile duct/pancreas to 42 degrees C or more, there was a strong positive correlation between maximum output of RF energy and maximum temperature of tumors (r = 0.839, P less than 0.001). The antitumor effect of RF hyperthermia was augmented with increasing output of RF energy. Therefore, the maximum level of RF output may be a useful index for expressing the heating efficiency with respect to intra-abdominal deep-seated tumors.     

Hyperthermia in eccentrically located pelvic tumors: excessive heating of the perineal fat and normal tissue temperatures

Regional hyperthermia in deep-seated tumors can be limited by excessive heating of normal tissues, usually associated with pain or local discomfort. In this report, 57 hyperthermia treatments in 8 patients with locally advanced presacral recurrences of colorectal cancer were analyzed with respect to normal tissue temperatures, especially with respect to the perineal fat temperature. In 27 treatments, 1 to 2 catheters had been inserted from the perineal region through a large part of the perirectal and presacral fat into the tumor, so that temperature profiles of the perineal fat could be obtained. The mean maximum temperature (+/- SD) of the vagina, rectum, bladder, muscle tissue, and perineal fat was 40.8 +/- 1.2 degrees C, 40.9 +/- 1.6 degrees C, 40.5 +/- 1.6 degrees C, 39.8 +/- 0.7 degrees C, and 42.6 +/- 1.1 degrees C, respectively. The mean maximum systemic temperature (+/- SD) was 37.7 +/- 0.7 degrees C. In 42% of the treatments, the temperature in the perineal fat ranged between 43 and 46 degrees C and was treatment-limiting. In conclusion, overheating of the perineal fat is a problem in the treatment of eccentrically located tumors of the presacral region when relatively high temperatures in the tumor will be maintained for longer time periods.     

Sequential activation of multiple grounding pads reduces skin heating during radiofrequency tumor ablation.

PURPOSE: Radiofrequency (RF) tumor ablation has become an accepted treatment modality for tumors not amenable to surgery. Skin burns due to ground pad heating may become a limiting factor for further increase in ablation zone dimensions and generator power. We investigated a method were groups of ground pads are sequentially activated to reduce skin heating. METHODS: We compared conventional operation (i.e. simultaneous connection of all pads) to sequentially switched activation of the pads where different pad combinations are active for periods of approximately 0.3 - 8 s. The timing during sequential activation was adjusted to keep the leading edge temperature equal between the pads. We created Finite Element Method computer models of three pads (5 x 5 cm, 1 cm apart) placed in line with the RF electrode on a human thigh to determine differences in tissue heating during simultaneous and sequential ground pad activation. We performed experiments with three ground pads (5 x 10 cm, 4 cm apart) placed on a tissue phantom (1.5 A, 12 min) and measured pad surface and leading edge temperatures. RESULTS: Temperature rise below the leading edge for proximal, middle and distal ground pad in relation to active electrode location was 5.9 degrees C +/- 0.1 degrees C, 0.8 degrees C +/- 0.1 degrees C and 0.3 degrees C +/- 0.1 degrees C for conventional operation, and 3.3 degrees C +/- 0.1 degrees C, 3.4 degrees C +/- 0.2 degrees C and 3.4 degrees C +/- 0.2 degrees C for sequentially activated operation in the experiments (p < 0.001). CONCLUSION: Sequential activation of multiple ground pads resulted in reduced maximum tissue temperature. This may reduce the incidence of ground pad burns and may allow higher power RF generators.