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Biomedical subjects

K H Luk

Publications and source records attributed to K H Luk.

48 records · Page 3Linked to original sources
PubMed1975

Evaluation of time-dose factors in glottic tumors.

Sixty patients with localized squamous cell carcinoma of the vocal cord without nodal or metastatic disease were treated with four fractions per week. No serious complications occurred with the dose and fractionation schedule as outlined. Voice quality after treatment has been satisfactory. After a minimum of two years follow-up the control rates for T1 and T2 tumors are 80% and 81.5%, respectively. All radiation therapy failures were cured surgically. A dose-response curve was constructed for T1 lesions, utilizing the Ellis' formula to derive the NSD, from data from different therapy centers. There appears to be no differences in the parameters studied between four and five fractions per week treatment schedules. A ret dose of approximately 1800 appears somewhat low for optimal control rates in T1 and T2 tumors.

Carcinoma, Squamous Cell↗
PubMedDate not supplied

Thermographically determined specific absorption rate patterns of 434-MHz applicators.

The specific absorption rate (SAR) patterns of two 434-MHz hyperthermia applicators, models TCA 434-1 (9 X 20 cm) and TCA 434-2 (13 X 25 cm), were evaluated thermographically using a phantom model. The phantom model consisted of a 2-cm-thick layer of fat and a 10-cm depth of muscle contained in a 30 X 30 cm base Plexiglas box. The model was bisected in the middle. Polyester screens at the interface allowed the synthetic gel to make electrical contact between the two halves of the muscle tissue. Octyl alcohol was applied to the fat interface to ensure continuity of dielectric properties. Thermograms were taken for both applicators over the following areas of the exposed model: (1) fat surface, (2) internal surface with E-field parallel to interface, and (3) internal surface with E-field perpendicular to interface. SAR's were calculated from the temperature rise (8 degrees C maximum), net input power (550-650 W), exposure time (15-60 s), and specific heat of the muscle (0.86 kcal/kg degrees C). A factor of 0.42 needs to be multiplied to correct for the specific heat of fat. High localized SAR's along the broad sides of the applicators were seen when the applicators were in direct contact with the phantom. With the use of a 0.8-cm polystyrene foam spacing, the SAR's within the aperture of the applicators were relatively uniform. The patterns of the two applicators were quite similar. However, the TCA 434-1 applicator is smaller and more applicable for clinical conditions.

Absorption↗
PubMedDate not supplied

Evaluation of captive bolus applicators.

Three square (L, M, MS) and one rectangular (HN) applicators with captive boluses were provided by the Clini-Therm Corporation for evaluation. Surface cooling is achieved by attaching a mineral oil captive bolus to the built in water-circulating tubes at the aperture of the applicators. These applicators were tested on a phantom with a 2-cm fat slab over 10-cm-thick muscle. Surface and sagittal heating patterns were obtained using a thermograph. All captive-bolus applicators have heating patterns similar to that of the regular Clini-Therm applicators. Due to hot spots at the edges of the applicators where the E fields terminate, these modified applicators should not be placed in direct contact with patients when boluses are not used. Tests with Clini-Therm regular water bolus instead of the captive oil bolus indicated that the orientation of water flow should be parallel to the E field to minimize perturbation of the heating patterns. Thermal conduction studies showed that the captive bolus reacts too slowly for skin temperature control. The modified captive bolus applicators did not improve the performance of the system.

Adipose Tissue↗
PubMedDate not supplied

Heating patterns of microwave applicators in inhomogeneous arm and thigh phantoms.

Heating rate (HR) patterns in cylindrical structures were studied with inhomogeneous limb phantoms. These phantoms, arm and thigh models consisting of fat, bone, and muscle material, were heated with Clini-Therm L, M, and MS applicators at 915 MHz. The thigh model is 18 cm in diameter with 2.65-cm-thick fat on the outside and a 4-cm-diam bone in the center. The arm model is 9 cm in diameter with 1.35-cm-thick fat and 2-cm-diam bone. All models are 29 cm long with phantom muscle in the space between fat and bone and were heated with their long axes parallel or perpendicular to the E field. HR patterns in the transverse and longitudinal planes were obtained thermographically. A large water bolus, with the water channels parallel to the E field, was used in every case. In the thigh model, maximum heating was in the muscle for both L and M applicators when the E field was parallel to the long axis. When it was perpendicular, the maximum heating occurred in the fat layer. However, the peak HR in the fat remained about the same for both E field orientations. For the small applicator, heating was mostly in the fat, and the two field orientations did not cause much difference in the heating pattern. In the arm model, the maximum heating of all three applicators occurred mostly in the muscle for both E-field orientations. However, the maximum HR was reduced by a factor of 2 to 3 when the E field was perpendicular rather than parallel to the long axis.(ABSTRACT TRUNCATED AT 250 WORDS)

Arm↗
PubMedDate not supplied

Perturbations due to the use of catheters with non-perturbing thermometry probes.

Perturbations due to the use of catheters with non-perturbing thermometry probes were investigated in static phantom at 915 MHz. Fibre optic probes for the Luxtron and Clini-Therm thermometry systems, and Vitek probes for the BSD hyperthermia systems, were inserted in closed-end catheters at depths up to 2 cm in the phantom and exposed parallel to the E-field. The probes alone produced 0-12 per cent changes in heating and catheters alone were 0-20 per cent. When the probes were inserted in catheters, perturbations were 0-12 per cent at the surface and 1 cm depth, and 5-15 per cent at 2 cm depth. Even with non-perturbing probes it is important to place catheters perpendicular to the E-field during microwave hyperthermia.

Electromagnetic Fields↗
PubMedDate not supplied

Changes in heating patterns due to perturbations by thermometer probes at 915 and 434 MHz.

The changes in heating patterns due to perturbations by thermometer probes in microwave fields were investigated in static phantoms at 915 and 434 MHz. Thermograms taken parallel to the plane of E and H fields, at depths of up to 2 cm, indicated heating changes of +25 to -45 per cent at 915 MHz and +/- 15 per cent at 434 MHz. The amount of perturbation is dependent on the length, size and location of the probes in the RF fields and their orientations to the electric field. If proper probe placement techniques are not observed when metallic probes are involved, hot and cool spots can be generated and shifted to sites that are not measured. Therefore misleading temperatures can result when changes in heating patterns are not detected. Perturbation also varies with applicator designs and phantom geometry. If thermistors and thermocouples are used, the effects of perturbation should be investigated with individual applicators under applicable clinical conditions.

Hyperthermia, Induced↗
PubMedDate not supplied

Changes in heating patterns of interstitial microwave antenna arrays at different insertion depths.

The changes in heating patterns of interstitial microwave antennas at different insertion depths were investigated in a static phantom at 915 MHz. Antennas for the Clini-Therm Mark VI system were inserted 5-15 cm into muscle-equivalent material, through nylon catheters. The phantom was heated with arrays of antennas at 2 cm spacings for 60 s at 15 W per antenna. Midplane and transverse heating patterns were determined thermographically with the antennas inserted parallel or perpendicular to the split of the phantom. Hot spots, independent of heating near the junction plane, were observed in the midplane of the 2 x 2 and 2 x 4 arrays at 2.8 cm from the insertion end. The magnitudes of these hot spots were reduced by 40-45 per cent as insertion depth was increased from 7 to 10.5 cm. With insertion depths of more than 11.5 cm the hot spots gradually diminished and heating occurred mostly near the junction plane. The observed heating patterns were caused by changes in impedance of the antenna arrays at different insertion depths. The impedance mismatch had resulted in different wave propagation within the tissue material which produced different radiation patterns. During treatments, because heating varies with insertion depth, great care must be exercised in monitoring temperatures.

Biomedical Engineering↗
PubMedDate not supplied

Intracavitary hyperthermia applicators for treating nasopharyngeal and cervical cancers.

Many intracavitary microwave applicators have been designed to heat tissues along the side of an antenna. For tumours in nearly closed-end cavities such as the nasopharynx and cervix, heating near the tip of the applicators is necessary for effective treatment. A nasopharyngeal applicator made of Micro Coax UT-250A and a cervical applicator made of RG-9/U cables were designed to provide heating at the tip. Return losses of 8-12 dB were obtained at 915 MHz by varying the size of two metal sleeves and adjusting the distance between these sleeves and the reflectors at the applicator tips. Heating patterns were evaluated on a muscle phantom with a thermograph. At 915 MHz, maximum heating rates of 1.3 and 0.85 degrees C/W-min, respectively, were observed near the tip of the nasopharyngeal applicator and at its first sleeve opening. When operated at 915 MHz the cervical applicator has a maximum heating rate of 0.25 degrees C/W-min at the tip. Clinically, both applicators require a maximum power of 30 W to provide effective heating. This makes it possible to provide intracavitary hyperthermia at rural hospitals and small clinics with a small portable system.

Biomedical Engineering↗
PubMedDate not supplied

Design of intracavitary microwave applicators for the treatment of uterine cervix carcinoma.

A 915 MHz intracavitary applicator was designed to heat tumours in the cervical and upper vaginal regions. The applicator has a 3.5-turn helical coil wound around the distal 19 mm of a dielectric rod 43 mm long and 30 mm in diameter. For treating uterine cancer, a 2450 MHz, 4 mm diameter helical applicator was made by replacing 6 cm of the outer conductor of a coaxial cable with six turns of copper wire soldered to the outer conductor. The heating patterns were determined thermographically in a muscle phantom. The maximum heating rates were 0.42 and 0.83 degrees C/W-min, respectively, for the 915 and 2450 MHz applicators. Intracavitary temperature distributions in the upper vagina, cervix and uterus were measured at the surface of the applicators with thermocouples. The average temperature was 46.0 +/- 2.1 degrees C (S.D.) at mid-tumour and 44.5 +/- 0.8 degrees C at the tumour periphery. The maximum temperature, up to 51.5 degrees C, was measured at the surface of the cervical applicator. The majority of the patients (28/30) tolerated the investigational treatment without burns or pain. Rectal temperatures were also monitored. The location of the hot-spot (40.7 degrees C) in the rectum, 5-7 cm above the anus, corresponded to the tip of the cervical applicator (47.1 degrees C).

Diathermy↗