An efficient numerical technique for bioheat simulations and its application to computerized cryosurgery planning
Introduction
Simulation of heat transfer problems involving phase change is of great importance in the study of thermal injury to biological systems. One of the most relevant examples is cryosurgery, which is the intentional destruction of undesired biological tissues by freezing [1]. Modern cryosurgery is frequently performed as a minimally-invasive procedure, with the application of a large number of cooling probes (cryoprobes), in the shape of long hypodermic needles, strategically located in the area to be destroyed (the target region) [2]. Here, the reconstruction of the target region, as well as monitoring of the freezing process, must be performed by means of imaging devices such as ultrasound or MRI [3], [4], [5], [6].
The clinical application of cryosurgery is not without technical difficulties, some of which are related to planning and control of a large number of cryoprobes, while others are related to the quality and limitations of imaging techniques. The long-term benefit of cryosurgery is not only affected by those technical difficulties, but also by the specific thermal history forced upon the tissue, the unique response of the tissue to low temperature exposure, and possibly the presence of drugs that sensitize that tissue to injury at low temperatures [7].
Since temperature can be measured only at discrete points in the target region, simulation of heat transfer is an extremely useful tool in developing and improving cryosurgical techniques [8], [9], [10], [11]. Here, heat transfer simulations can be calibrated with temperature measurements in the target tissue for the purpose of parametric estimation of tissue properties [12]. Heat transfer simulations can also assist in evaluating the certainty in temperature measurements, as has been demonstrated for the application of hypodermic thermocouples during cryosurgery [13]. Heat transfer simulations can also be used to augment imaging in real time, by identifying specific temperature thresholds within the frozen region [14]. However, one must bear in mind that the quality of those simulations relies on the certainty of the available values of the thermophysical properties of the tissue [15].
As a part of an ongoing project to develop an automated planning tool for cryosurgery, the current study is aimed at developing a numerical scheme which significantly reduces the heat transfer simulation run time; the duration of simulation has been identified as a critical factor in making that tool clinically relevant. Prior work on this ongoing project focused on the development of a force-field analogy technique, which executes a series of heat transfer simulations and automatically relocates cryoprobes between every two consecutive runs, until an optimum cryoprobe layout is found [16], [17]. Prior work also included the development of an algorithm to predict the best initial condition for the force-field analogy procedure (termed “bubble-packing”), in order to decrease the number of heat transfer simulations required in the force-field analogy process [18]. Finally, prior work included the development of the cryoheater, a self-controlled electrical heater, which helps to limit freezing injury to the target region [19]. Consistent with previous work, the new technique is demonstrated on a geometrical model of a prostate, where prostate cryosurgery is a common minimally-invasive procedure.
Section snippets
Mathematical formulation
Bioheat transfer in this study is modeled with the classic bioheat equation [20]:where C is the volumetric specific heat of the tissue, T the temperature, t the time, k the thermal conductivity of the tissue, the blood perfusion volumetric flow rate per unit volume of tissue, Cb the volumetric specific heat of the blood, Tb the blood temperature entering the thermally treated area, and is the metabolic heat generation. Numerous scientific reports have
Application to computerized planning of cryosurgery
While the numerical scheme presented above is quite general, the main objective for its development is to accelerate numerical simulations of cryosurgery, in order to make previously established planning algorithms practical [17], [18]. The objective in cryosurgery is to maximize freezing damage internal to the target region while minimizing freezing damage external to the target region. Consistent with prior work, a target region area is defined by the outer contour of the prostate, excluding
Results and discussion
The new numerical scheme has been analyzed in 1D, 2D, and 3D, to study its various characteristics. The prostate model used in the 2D and 3D cases has been reconstructed from a set of ultrasound images which were made available by the Robarts Imaging Institute, London, Ontario, Canada [25] for the purpose of the current study. The prostate images were segmented manually at our laboratory in order to reconstruct a full 3D target region. Since the ultrasound image data was not obtained during
Summary and conclusions
As a part of an ongoing project to develop an automated tool for cryosurgery planning, the current study presents a numerical scheme that significantly reduces the heat transfer simulation run time, which has been identified as a limiting factor in making this tool clinically relevant. The new numerical scheme is a modification of an early numerical scheme, in which modification is focused on variable grid and time intervals. Prior work focused on the development of a force-field analogy
Acknowledgements
This project is supported by the National Institute of Biomedical Imaging and Bioengineering (NIBIB)—NIH, grant #R01-EB003563-02,03. The authors would like to thank Dr. Aaron Fenster from the Robarts Imaging Institute, London, Ontario, Canada, for providing ultrasound images of the prostate.
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