AbstractThe charring tissue generated by the high temperature during microwave ablation can affect the therapeutic effect, such as limiting the volume of the coagulation zone and causing rejection. This paper aimed to prevent tissue carbonization while delivering an appropriate thermal dose for effective ablations by employing a treatment protocol with real-time bioelectrical impedance monitoring.

微波消融过程中高温产生的炭化组织会影响治疗效果，例如限制凝固区的体积并引起排斥反应。本文旨在通过采用具有实时生物电阻抗监测的治疗方案来防止组织碳化，同时提供适当的热剂量以进行有效消融。

Firstly, the current field response under different microwave ablation statuses is analyzed based on finite element simulation. Next, the change of impedance measured by the electrodes is correlated with the physical state of the ablated tissue, and a microwave ablation carbonization control protocol based on real-time electrical impedance monitoring was established.

首先，基于有限元仿真分析了不同微波烧蚀状态下的电流场响应。接下来，将电极测量的阻抗变化与消融组织的物理状态相关联，并建立了基于实时电阻抗监测的微波消融碳化控制协议。

The finite element simulation results show that the dielectric properties of biological tissues changed dynamically during the ablation process. Finally, the relative change rule of the electrical impedance magnitude of the ex vivo porcine liver throughout the entire MWA process and the reduction of the central zone carbonization were obtained by the MWA experiment.

有限元模拟结果表明，生物组织的介电性能在消融过程中动态变化。最后，通过MWA实验获得了离体猪肝在整个MWA过程中电阻抗幅度的相对变化规律以及中心区碳化的减少。

Charring tissue was eliminated without water cooling at 40 W and significantly reduced at 50 W and 60 W. The carbonization during MWA can be reduced according to the changes in tissue electrical impedance to optimize microwave thermal ablation efficacy..

碳化组织在40 W时无需水冷即可消除，在50 W和60 W时显着减少。可以根据组织电阻抗的变化减少MWA期间的碳化，以优化微波热消融功效。。

IntroductionMicrowave ablation (MWA), known for its broad ablation range, wide indications, and minimal heat deposition effect, has been widely used in treating solid tumors such as liver tumors1,2,3,4. In MWA, direct energy deposition in the ablation zone leads to elevated temperatures in surrounding tissues.

引言微波消融（MWA）以其广泛的消融范围，广泛的适应症和最小的热沉积效应而闻名，已被广泛用于治疗实体瘤，如肝肿瘤1,2,3,4。在MWA中，消融区的直接能量沉积导致周围组织的温度升高。

The ablated zone is prone to carbonization, resulting in dehydrated carbonized tissue. The “carbonized” zone is close to the antenna axis, at higher temperatures, the tissue appears charred, highly desiccated, and black. A more peripheral zone of complete thermal denaturation of proteins is known as “white coagulation”5.

消融区容易碳化，导致碳化组织脱水。“碳化”区域靠近天线轴，在较高温度下，组织会出现烧焦，高度干燥和黑色。蛋白质完全热变性的更外围区域被称为“白色凝固”5。

Previous studies have shown that in the MWA of some organs, such as the spleen6, the crushing and avulsion of charring tissues in the course of needle withdrawal can cause bleeding. Carbonized tissue impedes heat dispersion, causing the ablation zone to adopt an ellipsoidal shape rather than spherical7.

先前的研究表明，在某些器官（如脾脏）的MWA中，拔针过程中炭化组织的挤压和撕脱会导致出血。碳化组织阻碍热扩散，导致消融区采用椭球形状而不是球形7。

The carbonization phenomenon may also induce both regional and systemic inflammatory responses and other unwanted side effects8,9,10. Precise control of microwave output for ablating tumors effectively while avoiding tissue carbonization is important for clinical MWA.Researchers propose minimally invasive thermometry to prevent carbonization by inserting single-point or multipoint thermometry needles for local temperature measurement11,12.

碳化现象也可能诱发区域和全身炎症反应以及其他不必要的副作用8,9,10。精确控制微波输出以有效消融肿瘤，同时避免组织碳化对于临床MWA很重要。研究人员提出微创测温法，通过插入单点或多点测温针进行局部温度测量来防止碳化11,12。

Ultrasound-based thermometry remains insufficient for deep temperature field distribution measurement in liver tissue13. Additionally, the degree of tissue inactivation, as per the kinetic properties of thermal injury in biological tissues, necessitates evaluation based on temperature and exposure duration, indicating that assessing tissue ablation efficacy solely based on temperature is insufficient14,15.

基于超声波的温度计仍然不足以测量肝组织中的深部温度场分布13。此外，根据生物组织热损伤的动力学特性，组织失活的程度需要基于温度和暴露持续时间进行评估，这表明仅基于温度评估组织消融效果是不够的14,15。

Some r.

一些r。

(1)

(1)

where µ is the magnetic permeability, σ is the conductivity, ε is the relative dielectric permittivity, and E is the electric field strength.The Pennes heat transfer equation is expressed as:$$\rho C\frac{{\partial T}}{{\partial t}}=\nabla (k\nabla T)+{Q_{{\text{ext}}}}$$

其中µ是磁导率，σ是电导率，ε是相对介电常数，E是电场强度。Pennes传热方程表示为：$$$\ rho C \ frac{{\ partial T}}{\ partial T}=\ nabla（k \ nabla T）+{Q \ uu{\ text{ext}}$$

(2)

(2)

where ρ is the density, C is the specific heat capacity, k is the thermal conductivity, and Qext is the external heat source. Qext is microwave energy absorbed by biological tissues, and a process of converting microwave energy into thermal energy can be expressed as:$${Q_{{\text{ext}}}}=\frac{{\sigma {{\left| E \right|}^2}}}{2}$$.

其中ρ是密度，C是比热容，k是导热系数，Qext是外部热源。Qext是生物组织吸收的微波能量，将微波能量转换为热能的过程可以表示为：$${Q{\ text{ext}}}=\frac{\ sigma{\ left | E \ right |}^ 2}}{2}$$。

(3)

(3)

Set the simulation parameters. It mainly includes the dielectric property parameters, the biological heat conduction parameters of liver tissue, and the material parameters of the MWA antenna. The thermal conductivity (k), density (ρ), relative dielectric permittivity (ε), conductivity (σ), and specific heat capacity (C) of the liver are as follows24:$$k(T)=\left\{ \begin{array}{l} 0.512;\; 293.15\; K \leq T \leq 363.15\; K \hfill \\ 0.2027\; T - 17.933;\; 363.15\; K<T \leq 373.15\; K \\ 0.0053\; {T^2} - 1.727\; T+64.681;\; 373.15\; K<T \leq 386.15\; K \\ 0.21;\; 386.15\; K <T \leq 473.15\; K \hfill \\ \end{array} \right.$$.

设置模拟参数。它主要包括介电性能参数，肝组织的生物热传导参数以及MWA天线的材料参数。肝脏的热导率（k），密度（ρ），相对介电常数（ε），电导率（σ）和比热容（C）如下24：$$k（T）=\ left \ \ begin{array}{l}0.512；\；293.15英寸；K\leq T\leq 363.15 \；K\h填充\\ 0.2027 \；T-17.933；\；363.15英寸；K<T\leq 373.15 \；K\\0.0053 \；{T^2}-1.727 \；电话+64.681；\；373.15英寸；K<T\leq 386.15 \；K\\0.21；\；386.15英寸；K<T\leq 473.15 \；K\h填充\ \结束{数组}\右。$$。

(4)

(4)

$$\rho (T)=\left\{ \begin{array}{l} 1050;\quad 293.15\; K \leq T \leq 373.15\; K \hfill \\ 294;\quad 373.15\; K<T \leq 473.15\; K \end{array} \right.$$

$$\ rho（T）=\左\{\开始{数组}{l}1050；\quad 293.15英寸；K\leq T\leq 373.15 \；填充294；\四联373.15英寸；K<T\leq 473.15 \；K \结束{数组}\正确$$

(5)

(5)

$$\begin{aligned} \varepsilon (T)&=48.391\left\{ {1 - \frac{1}{{1+\exp [0.0764(82.271 - T+273.15)]}}} \right\} \\ &\quad +1;\; 293.15\; K \leq T \leq 473.15\; K \end{aligned}$$

$$\开始{对齐}\varepsilon（T）&=48.391 \左{1-\frac{1}{1+\exp[0.0764（82.271-T+273.15）]}}\右；293.15英寸；K\leq T\leq 473.15 \；K \结束{对齐}$$

(6)

(6)

$$\begin{aligned} \sigma (T)&=2.713\left\{ {1 - \frac{1}{{1+\exp [0.0697(85.375 - T+273.15)]}}} \right\}; \\ &\quad 293.15{\text{ }}K \leq T \leq 473.15{\text{ }}K \end{aligned}$$

$$\开始{对齐}\ sigma（T）&=2.713 \左\{{1-\ frac{1}{{1+\ exp[0.0697（85.375-T+273.15）]}}\右\；\ \&\四元组293.15{\文本{}}K \ leq T \ leq 473.15{\文本{}}K \结束{对齐}$$

(7)

(7)

$$C(T)=\left\{ \begin{array}{l} 3600;\; 273.15\; K \leq T \leq 373.15\; K \hfill \\ 327800;\; 373.15\; K<T \leq 378.15\; K \hfill \\ 2103;\; 378.15\; K<T \leq 473.15\; K \end{array} \right.$$

$$C（T）=\left\{\begin{array}{l}3600；\；273.15\;K\leq T\leq 373.15；327800韩元；373.15\;K<T\leq 378.15\；K\hfill 2103；378.15\;K<T\leq 473.15\；K\end{array}\right$$

(8)

(8)

The dielectric property parameters and tissue heat conduction parameters used in the simulation model are shown in Table 219,24.Table 2 Parameters used in the simulation model.Full size tableStep 2: Set the current field control equations under impedance measurement. This results in minimal conduction current and negligible magnetic field generation due to the low frequency, which allows for considering a quasi-static electric field without compromising engineering calculation accuracy.

模拟模型中使用的介电性能参数和组织热传导参数如表219、24所示。表2模拟模型中使用的参数。全尺寸表步骤2：在阻抗测量下设置电流场控制方程。由于频率较低，这导致最小的传导电流和可忽略的磁场产生，这允许在不影响工程计算精度的情况下考虑准静态电场。

When the current with angular frequency\(\omega\)is applied, the mathematical equation is expressed as:$$\left\{ \begin{array}{l} \nabla \cdot ((\sigma +j\omega \varepsilon )\nabla \varphi )=0 \hfill \\ \delta =\sigma +j\omega \varepsilon \hfill \\ \end{array} \right.$$.

当施加角频率电流（ω）时，数学方程表示为：$$左{开始{数组}{l}\ nabla \ cdot（（\sigma+j \ω\ varepsilon）\nabla \ varphi）=0 \ hfill \ \ delta=\sigma+j \ω\ varepsilon \ hfill \ \ end{数组}\右。$$。

(9)

(9)

where j denotes the vector sign,\(\delta\)is the complex conductivity, and\(\varphi\)is the potential.The Dirichlet boundary condition is defined as:$$\varphi (x,y)=f(x,y)\quad (x,y) \in \partial \Omega$$

其中j表示矢量符号，\（\ delta \）是复数电导率，\（\ varphi \）是电势。Dirichlet边界条件定义为：$$\ varphi（x，y）=f（x，y）\ quad（x，y）\ in \ partial \ Omega$$

(10)

(10)

The Neumann boundary condition is defined as:$$- \delta (x,y)\frac{{\partial \varphi (x,y)}}{{\partial n}}=J(x,y) \quad (x,y) \in \partial \Omega$$

Neumann边界条件定义为：$$-\ delta（x，y）\frac{\ partial \ varphi（x，y）}}{\ partial n}=J（x，y）\ quad（x，y）\ in \ partial \ Omega$$

(11)

(11)

where ∂Ω is the boundary of the field, f is the Dirichlet boundary condition function, and n is the direction of the normal outside the boundary.The articulation condition of the sub-interface within the field is expressed as:$${\delta _1}\frac{{\partial {\varphi _1}}}{{\partial n}}={\delta _2}\frac{{\partial {\varphi _2}}}{{\partial n}}$$.

其中∂Ω是场的边界，f是Dirichlet边界条件函数，n是边界外法线的方向。字段内子接口的连接条件表示为：$${\ delta \u 1}\ frac{\ partial{\ varphi \u 1}}{\ partial n}={\ delta \u 2}\ frac{\ partial{\ varphi \u 2}}{\ partial n}}$$。

(12)

(12)

Setting up the current field control equations, including the boundary conditions, calculated the potential value. The impedance value was also derived since the current was used as an excitation source.Step 3: Set the microwave frequency (2450 MHz), ablation power, and ablation time to start the MWA simulation.

建立电流场控制方程，包括边界条件，计算电位值。由于电流被用作激励源，因此还导出了阻抗值。步骤3：设置微波频率（2450 MHz），消融功率和消融时间以开始MWA模拟。

Due to the probe’s limited spatial coverage and the minimal impact of electrode size on the current field compared to electrode spacing was kept at a constant length. Electrodes A1–A2 were spaced 26 mm apart, electrodes B1–B2 were spaced 18 mm apart, and electrodes C1–C2 were spaced 10 mm apart. The excitation electrode frequency was set to 20 kHz, and the current magnitude was 0.5 mA in this paper25.For enhanced visualization of differences, the magnitude of measured impedances under different excitation electrodes is shown in Fig. 2.

由于探针的空间覆盖范围有限，并且与电极间距相比，电极尺寸对电流场的影响最小，因此保持恒定长度。电极A1-A2间隔26毫米，电极B1-B2间隔18毫米，电极C1-C2间隔10毫米。本文将激发电极频率设置为20 kHz，电流幅度为0.5 mA。为了增强差异的可视化，不同激发电极下测量阻抗的幅度如图2所示。

For example, in Fig. 2, when A1–A2 are set as the excitation electrodes, the measured impedances are obtained for electrodes B1–B2 and C1–C2, respectively. The simulation results also showed that the impedance measurements at the moments of 120 s, 150 s, and 180 s were different and showed an increasing trend with time, i.e., the electrical properties of different ablation zone states influence the potential distribution.

例如，在图2中，当将A1–A2设置为激发电极时，分别获得电极B1–B2和C1–C2的测量阻抗。仿真结果还表明，120 s，150 s和180 s时刻的阻抗测量值不同，并且随着时间的推移呈现出增加的趋势，即不同烧蚀区状态的电特性会影响电位分布。

Additionally, the differences in impedance changes between different electrode pairs may be due to the different positions in which they are located.Fig. 2Impedance magnitudes with various excitation electrodes.Full size imageSystem for measuring bioelectrical impedance during MWAAs shown in Fig. 3, the MWA system is composed of a microwave solid state source (Bada Microwave Technology Co., Ltd., Hangzhou, China), a microwave ablation antenna (Kangyou Medical Instruments, Nanjing, China), a person.

另外，不同电极对之间阻抗变化的差异可能是由于它们所在的位置不同。图2各种激发电极的阻抗大小。用于测量MWAA期间生物电阻抗的全尺寸成像系统如图3所示，MWA系统由微波固态源（巴达微波技术有限公司，中国杭州），微波消融天线（康友医疗器械，南京，中国），一个人。

(13)

(13)

$$\text{S}\text{N}\text{R}=10{\log _{10}} \left(\frac{{\sum\nolimits_{m} {v_{{i,j}}^{2}} }}{{\sum\nolimits_{m} {{{({v_{i,j}} - {{\bar {v}}_{i,j}})}^2}} }} \right)$$

$$\text{S}\text{N}\text{R}=10{\log{10}}\left（\frac{\sum\nolimits\uu{m}{v\u{{{i，j}}^{2}}}}{\sum\nolimits\u{{{{{{v\u{i，j}}-{\bar{v}}}{i，j}}^ 2}}}}\右）$$

(14)

(14)

where\({v_{i,j}}\)denotes the voltage value acquired on the jth pair of electrodes when the ith pair of electrodes is excited, and m denotes the number of acquisition frames (m = 50). \({\bar {v}_{i,j}}\)denotes the average value of the repetitively acquired voltage of the corresponding channel.The average RSD of the measurement results below 0.04% and an average SNR of 70 dB or higher are good enough for impedance measurements, as shown in Fig. 4a and b.

其中\（{v{i，j}}\）表示当第i对电极被激发时在第j对电极上获得的电压值，m表示采集帧数（m=50）\（{\bar{v}_{i，j}}\）表示相应通道重复获取的电压的平均值。测量结果的平均RSD低于0.04%，平均SNR为70 dB或更高，足以进行阻抗测量，如图4a和b所示。

So, the hardware provides good acquisition accuracy and reliable impedance detection.Fig. 4(a) Measurement results of RSD. (b) Measurement results of SNR.Full size imageElectrical impedance measurement during MWAAs shown in Fig. 5a, the structural section of the bioelectrical impedance probe was devised in this study.

因此，硬件提供了良好的采集精度和可靠的阻抗检测。图4（a）RSD测量结果。（b）SNR测量结果。全尺寸图像电阻抗测量在MWAA期间如图5a所示，本研究设计了生物电阻抗探针的结构部分。

Six electrodes (blue) were added near the insulating medium sleeve of the microwave ablation antenna. Initially, a transparent heat-shrinkable tube layer was applied to the rear end of the insulating medium sleeve. Subsequently, metal-copper electrodes were wound onto the heat-shrinkable tube’s surface, enabling the setup of excitation and measurement electrodes in six configurations (A1A2–B1B2, A1A2–C1C2, B1B2–A1A2, B1B2–C1C2, C1C2–A1A2, C1C2–B1B2).

在微波消融天线的绝缘介质套管附近添加了六个电极（蓝色）。最初，将透明热收缩管层施加到绝缘介质套管的后端。随后，将金属铜电极缠绕在热缩管的表面上，可以在六种配置（A1A2–B1B2，A1A2–C1C2，B1B2–A1A2，B1B2–C1C2，C1C2–A1A2，C1C2–A1A2，C1C2–B1B2）中设置激发和测量电极。

Next, the metal electrodes were connected to the bioelectrical impedance measurement circuit board.The current path traversed the ablated lesion zone, enabling precise characterization of local tissue status by measuring impedance changes. Typically, electrical impedance testing utilizes a four-electrode system to mitigate the contact impedance effects observed in a two-electrode system27,28.

接下来，将金属电极连接到生物电阻抗测量电路板。电流路径穿过消融的病变区，通过测量阻抗变化可以精确表征局部组织状态。通常，电阻抗测试利用四电极系统来减轻在两电极系统中观察到的接触阻抗效应27,28。

As shown in Fig. 5a, each can serve as excitation or measurement electrodes during a measurement cycle. Figure 5b shows the current injection at electrod.

如图5a所示，每个电极都可以在测量周期中用作激发或测量电极。图5b显示了电极上的电流注入。

Ex vivo porcine liver impedance measurement experiments during MWAFresh ex vivo porcine liver was obtained from the local slaughterhouse and used the same day. The experiment was carried out at a room temperature of 25 ℃. Before ablation, the microwave power was set to 40 W, 50 W, and 60 W, respectively, and the cumulative effective ablation duration was 360 s.

MWAFresh期间的离体猪肝阻抗测量实验从当地屠宰场获得离体猪肝，并在同一天使用。实验在25℃的室温下进行。消融前，微波功率分别设置为40 W，50 W和60 W，累积有效消融持续时间为360 s。

The water-cooling function of the microwave ablation antenna was not used in the experiment. An initial collection of electrical impedance magnitude preceded ablation. Intermittent pausing for 1 s per every 10 s of ablation aimed to simulate continuous mode effects closely, with impedance magnitude recorded during these pauses.

实验中未使用微波消融天线的水冷功能。消融之前最初收集的电阻抗幅度。每10秒消融间歇暂停1秒，旨在紧密模拟连续模式效应，并在这些暂停期间记录阻抗幅度。

Chapters 1 to 6 were also assigned to different excitation and measurement electrode configurations. Each ablation mode (continuous group and impedance group) involved in this article has been repeated four times (n = 4 for each condition) for a total of 24 groups of experiments to ensure the reliability and repeatability of the results.

第1章至第6章也被分配到不同的激发和测量电极配置。本文涉及的每种消融模式（连续组和阻抗组）已经重复了四次（每种条件n=4），总共进行了24组实验，以确保结果的可靠性和可重复性。

The final data were averaged. To minimize discrepancies arising from liver variability and probe placement, a variable representing the relative change in impedance magnitude pre- and post-ablation, the relative change magnitude of electrical impedance, was used as an index to determine the occurrence of carbonization.

最终数据取平均值。为了最大限度地减少肝脏变异性和探针放置引起的差异，使用代表消融前后阻抗幅度相对变化的变量，即电阻抗的相对变化幅度作为确定碳化发生的指标。

Available representing the relative change in impedance magnitude pre-ablation and post-ablation\({Z_{{\text{diff}}}}\)is defined as:$${Z_{{\text{diff}}}}=\frac{{{{Z^{\prime}}_{{\text{real}}}} - {Z_{{\text{real}}}}}}{{{Z_{{\text{real}}}}}}$$.

可用表示消融前和消融后阻抗幅度的相对变化（{Z{{{text{diff}}}}}）定义为：$${Z{{{text{diff}}}=\frac{{{{{Z ^{\ prime}}}u{{\ text{real}}}-{Z{{{\ text{real}}}}}{{{Z}{{\文本{实}}}}$$。

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(15)

where\({Z^{\prime}_{{\text{real}}}}\)is the electrical impedance magnitude at each time point after ablation, and \({Z_{{\text{real}}}}\)is the electrical impedance magnitude before ablation.ResultsChanges in electrical impedance of porcine liver during MWA under 40 WFigure 6a and f shows the temporal variation of the average electrical impedance magnitude and temperature of six measurement experiments with continuous ablation of the ex vivo porcine liver for 360 s at a microwave power of 40 W.

其中\（{Z ^{\ prime}}uuu{\ text{real}}}}）是消融后每个时间点的电阻抗幅度，而\（{Z{\ text{real}}}}）是消融前的电阻抗幅度。结果在40 W下MWA期间猪肝电阻抗的变化图6a和f显示了在40 W的微波功率下连续消融离体猪肝360 s的六个测量实验的平均电阻抗幅度和温度的时间变化。

The trend in each channel indicated primarily two notable increases in electrical impedance magnitude. During the pre-ablation period, the electrical impedance magnitude initially rises, peaks around 60 ℃, and then declines while the temperature ascends steadily. In the mid-ablation stage, the electrical impedance magnitude rapidly increases after briefly stabilizing at its nadir, while the temperature stabilizes at around 90% of its peak.

每个通道的趋势主要表明电阻抗幅度有两个显着增加。在预烧蚀期间，电阻抗幅度最初上升，在60℃左右达到峰值，然后随着温度的稳定上升而下降。在消融中期，电阻抗幅度在短暂稳定在最低点后迅速增加，而温度稳定在其峰值的90%左右。

Towards the ablation’s conclusion, the electrical impedance magnitude surges to higher resistance levels while the temperature nearly stabilizes at its peak. After pausing the ablation, the electrical impedance magnitude and temperature rapidly decrease from their peak values. The trend in electrical impedance magnitude exhibits resemblances to findings in the literature29,30,31.

对于消融的结论，电阻抗幅度激增到更高的电阻水平，而温度几乎稳定在其峰值。停止消融后，电阻抗幅度和温度从峰值迅速下降。电阻抗幅度的趋势与文献29,30,31中的发现相似。

Additionally, variations in electrical impedance magnitude and temperatures among liver tissue in each experimental group stemmed from discrepancies in the ex vivo porcine liver and the diverse placements of electrical impedance probes. Nonetheless, the majority of experiments progressed through the four ablations as mentioned above stages.Fig.

此外，每个实验组肝组织电阻抗大小和温度的变化源于离体猪肝的差异和电阻抗探针的不同放置。尽管如此，大多数实验都是通过上述四个阶段进行的。图。

6Trend of electrical impedance magnitude versus temperature over time for 6 channels. (a) Channel (1), (b) cha.

6 6个通道的电阻抗幅度与温度随时间的变化趋势。（a） 频道（1），（b）cha。

Data availability

数据可用性

The data that support the findings of this study are available upon request from the corresponding author.

支持本研究结果的数据可应通讯作者的要求提供。

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Download referencesAcknowledgementsThis work was supported in part by the National Major Scientific Instruments and Equipment Development Project Funded by National Natural Science Foundation of China under Grant 81827803, in part by the National Natural Science Foundation of China under Grant 82151311, in part by the Fundamental Research Funds for the Central Universities under Grant NP2024102, NJ2024016 and NJ2024029, in part by the Jiangsu Funding Program for Excellent Postdoctoral Talent under Grant 2024ZB661, and in part by the Nanjing University of Aeronautics and Astronautics Research and Practice Innovation Program under Grant xcxjh20230333.Author informationAuthors and AffiliationsDepartment of Electrical Engineering, College of Automation Engineering, Nanjing University of Aeronautics and Astronautics, Nanjing, 211106, ChinaXiao Zhang, Wei Wei & Lidong XingDepartment of Biomedical Engineering, College of Automation Engineering, Nanjing University of Aeronautics and Astronautics, Nanjing, 211106, ChinaLu Qian, Liuye Yao, Xiaofei Jin & Zhiyu QianKey Laboratory of Multi-modal Brain-Computer Precision Drive, Industry and Information Technology Ministry, Nanjing University of Aeronautics and Astronautics, Nanjing, 211106, ChinaXiao Zhang, Wei Wei, Lu Qian, Liuye Yao, Xiaofei Jin, Lidong Xing & Zhiyu QianAuthorsXiao ZhangView author publicationsYou can also search for this author in.

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PubMed Google ScholarContributionsZ. X., W. W., X. L., and J. X. were responsible for the ablation performance, conceptualization and methodology, and for the bioelectrical impedance system setup. Z. X. and Q. L. contributed to the MWA system and data analysis. Y. L. produced high-quality charts and graphs.

PubMed谷歌学术贡献。十、 ，W.W.，X.L。和J.X。负责消融性能，概念化和方法学，以及生物电阻抗系统设置。Z、 X.和Q.L.为MWA系统和数据分析做出了贡献。Y、 L.制作了高质量的图表。

X. L., J. X., and Q. Z. contributed to the review of the work critically for important intellectual content and final approval of the version to be published. All authors reviewed the manuscript.Corresponding authorsCorrespondence to.

十、 L.，J.X。和Q.Z.对重要的知识内容和即将出版的版本的最终批准做出了至关重要的贡献。所有作者都审阅了手稿。通讯作者通讯。

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The authors declare no competing interests.

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Additional information

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None of the experiments were performed on in vivo animals. All ex vivo porcine liver was chosen as the material for the experiment. Fresh ex vivo porcine liver was obtained from the local slaughterhouse and used the same day.

没有一个实验是在体内动物上进行的。选择所有离体猪肝作为实验材料。新鲜的离体猪肝是从当地屠宰场获得的，并在同一天使用。

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Reprints and permissionsAbout this articleCite this articleZhang, X., Wei, W., Qian, L. et al. Real-time monitoring of bioelectrical impedance for minimizing tissue carbonization in microwave ablation of porcine liver.

转载和许可本文引用本文Zhang，X.，Wei，W.，Qian，L。等人。实时监测生物电阻抗，以最大程度地减少猪肝微波消融中的组织碳化。

Sci Rep 14, 30404 (2024). https://doi.org/10.1038/s41598-024-80725-3Download citationReceived: 26 April 2024Accepted: 21 November 2024Published: 06 December 2024DOI: https://doi.org/10.1038/s41598-024-80725-3Share this articleAnyone you share the following link with will be able to read this content:Get shareable linkSorry, a shareable link is not currently available for this article.Copy to clipboard.

Sci Rep 1430404（2024）。https://doi.org/10.1038/s41598-024-80725-3Download引文收到日期：2024年4月26日接受日期：2024年11月21日发布日期：2024年12月6日OI：https://doi.org/10.1038/s41598-024-80725-3Share本文与您共享以下链接的任何人都可以阅读此内容：获取可共享链接对不起，本文目前没有可共享的链接。复制到剪贴板。

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KeywordsMicrowave ablationCarbonizationElectrical impedanceTemperature

关键词微波烧蚀碳化电阻温度